Non-invasive transcranial ultrasound apparatus

ABSTRACT

Disclosed is an autonomically functioning, battery-powered apparatus for non-invasive delivery of transcranial ultrasound. Insonation is directed by electronic circuitry and programmable instructions in memory and is modulated to achieve stereotemporal modulation of insonation so as to eliminate the need for assisted cooling. The apparatus is provided with registration members to facilitate stereotactic placement of transducer arrays and does not require diagnostic imaging guidance during setup and operation. Insonation is directed by electronic circuitry and programmable instructions in memory and is modulated to achieve stereotemporal modulation of insonation so as to eliminate the need for assisted cooling.

PRIORITY DOCUMENTS

This application claims the benefit of priority under 35 U.S.C. §119(e) from U.S. Provisional Patent Application Ser. Nos. 61/453,771, filed 17 Mar. 2011 and 61/390,149, filed 5 Oct. 2010; all said priority documents being incorporated herein in entirety by reference.

FIELD OF THE INVENTION

This invention is related to an autonomous, operator-independent, battery-powered ultrasound apparatus with electronic programmable actuation circuitry and stereotactic positioning features for non-invasive application of ultrasound.

BACKGROUND

Innovations in transcranial sonothrombolysis have been made by Alexandrov, Holland, Culp, Voorhees, Vortman, Chopra, Unger, Baron, Furuhata, Horzewski, Hansmann, Smith, Browning, Daffertshoffer, Lauer, and by others. However, all studies to date have been problematic in one way or another. The device of the invention differs from the devices used in the earlier CLOTBUST studies (Alexandrov et al 2004a & 2004b) and in studies by Sharma et al (2008a & 2008b) and Cintas (2002) in that those studies used a single diagnostic transducer unit manually operated by a sonographer to establish a preferred orientation, and the transducer unit was then typically locked into place using a cumbersome support frame. Alexandrov recently summarized the art in that, “One of major limitations of this technology that there are no reliable head frames for transducer fixation, and most studies are to be carried out hand-held” (Tsivgoulis 2007 J Clin Neurol 3:1-8). The head frames generally have a skeleton of surgical steel and are weighty and opaque to CT or MRI scanners.

Because the transducer units of the art must be carefully placed by sonographic imaging of the cerebral vasculature, generally with Doppler imaging, valuable time is lost. A solution to this problem as described here is to position a headset of the invention without diagnostic imaging as a guide, but instead by reference to guide, but instead using mechanical alignment guides by reference to external craniological landmarks and to use non-focused ultrasound transducers. Craniological landmarks are selected that define a reference plane tangential to the anterior and posterior cingulate processes, the reference plane with x, y and z coordinates, and thus the location of the cerebrovascular nexus where most strokes occur. The need for sonographer-controlled aiming is eliminated by preset angulation of each transducer relative to the external landmarks and the reference plane defined thereby.

Also consequent to the use of trained operators to set up devices for transcranial sonothrombolysis, there is in the art a general lack of consistency from operator to operator and from institution to institution. The reproducibility of transcranial ultrasound would be increased by provision for an autonomous apparatus that is configured to deliver a prescribed regimen of ultrasound with a fixed anatomical orientation. In order to relieve the need for a precise location of a clot, a solution to the problem of reproducibility is to provide multiple transducer arrays on a headset that is positioned as described above, so that the relationship of the transducer arrays to the cerebral vasculature is established by reference to external craniological landmarks, and to then insonate in a way that is generally safe, eliminating the need for a diagnostic study. In a preferred embodiment, the apparatus may be used where hemorrhage is present or is likely to occur, as is not infrequently the case in stroke and particular in stroke that has been treated with anticoagulants or thrombolytic drugs. In a first embodiment of the inventive apparatus, the autonomous insonation regime includes cyclical repetition of trains of pulses of ultrasound, where each cyclical repetition of pulse trains is a “metapulse” having a vectored and temporal distribution of individual pulse trains, with provision for alternating from transducer to transducer and limiting duty cycle so that no assisted cooling is required. The amplitude of ultrasound emitted by each transducer may be adjusted to compensate for differences due to transducer-to-transducer variability in manufacture, a technological advance in the art.

Portability remains a problem. Several features of the apparatus of the invention operate in synergy to enable the device to be transported with the subject without interrupting insonation. Alternatively the subject may walk while wearing the apparatus. By providing a lightweight power supply in a pocket-sized housing attached to the headset by a cable, the need for attachment to a stationary power supply is eliminated. Low power consumption for extended use is achieved by reducing the duty cycle of the insonation and by configuring emissions in the form of pulse trains having a pulse repetition frequency (PRF) and a pulse train repetition frequency (PTRF). Elimination of energy-consuming cooling means is made possible by alternating actuation of individual transducers at a cyclical frequency so that heat may dissipate during pulse intervals without need for assisted cooling, such as by fans or circulating coolant.

By making the headset from a lightweight and X-ray translucent material, and by configuring ultrasonic emissions from the headset transducer arrays for low power consumption, the apparatus becomes fully portable, may be transported with the patient, and operation of the apparatus need not be interrupted while the subject is, for example, inserted into a diagnostic machine for computerized tomography (CT). The option of beginning and continuing insonation while awaiting definitive diagnosis by angiographic CT is made possible by tethering the electronics and power supply away from the headset assembly at the end of a cable so that diagnostic imaging is not interfered with and by use of plastic structural members. Because transverse sections are commonly used in imaging to visualize the cerebral arterial nexii, in one embodiment the transducer array is mounted supracranially so that imaging may be performed without interference.

The option of portable extended delivery of transcranial ultrasound for sonothrombolysis has been a longstanding need but has not previously been realized. The apparatus of the invention is configured for continuous autonomous operation for 2 hrs, for 4 hours, for up to 12 hours, or for longer with intermittent operation, without operator intervention or recharge, and hence may be used non-invasively in stroke prophylaxis, as a follow-up to administration of thrombolytic drugs, and for other neurovascular conditions where persistent exposure to low amplitude ultrasound is desirable.

Tools for non-invasive sonothrombolysis, as known in the art, remain experimental, and have not yet resulted in changes to the basic standard of care for stroke or dramatically improved the prognosis. Recent clinical trials supplementing r-tPA with transcranial ultrasound resulted in an unacceptably high incidence of intracranial hemolysis (ICH) and the trials were stopped. Since then, no advance in the clinical use of transcranial sonothrombolysis has been reported.

Importantly, centralized stroke centers are currently available in only 3% of stroke cases, and mortality and morbidity following advanced diagnosis and treatment—absent sonothrombolysis—have improved by only 20% overall—even with the most advanced care. Each year in the United States, 700,000 strokes occur, more than 150,000 deaths are caused by strokes, and many strokes are debilitating for those who survive. Thus there is a need for new solutions and improvements in transcranial insonation that overcome the disadvantages described above. The risks of invasive treatments, administration of r-tPA among them, continue to outweigh potential benefits in the estimation of many physicians, and there is a long-felt and unmet need for an apparatus for stroke care having improved efficacy; an apparatus that is non-invasive, non-surgical, and safe.

SUMMARY

In a first embodiment, the device is an improved headset assembly for non-invasive transcranial ultrasound independent of operator control or adjustment and eliminating the need for imaging-guided placement or diagnostic study. The headset assembly is attached by a cable to a lightweight portable controller unit and battery power supply, and is configured for operator independent, autonomous operation with low power consumption.

Mounted on the headset assembly are a plurality of ultrasound transducers for acoustically engaging a head of a wearer. The headset is configured to be mounted circumcranially, and is provided with a registration system for stereotactically positioning the transducer arrays in contact with acoustic “windows” through the skull and directing the transducers to emit ultrasound onto the cerebral arteries most commonly associated with stroke. Conserved external craniological landmarks are used to position the headset with respect to the target cerebral vasculature.

Several problems in administering ultrasound transcranially have been identified and are addressed by this invention.

1. Because the apparatus is needed for portable operation during transport and may be most effective when providing continuous or intermittent insonation for 2, 4, or up to 12 hours or more, high power consumption and provision for assisted cooling (such as by fans or by circulating water jackets) is not possible. Using a duty cycle of 3-6% and spatial and temporal modulation of the transducers in the headset arrays, battery powered “hands-free” operation is possible for extended periods of time without operator intervention, up to 12 hrs or more, and assisted cooling is not required. 2. As disclosed here, stereotactic positioning using a combination of conserved craniological landmarks eliminates the need for a trained sonographer and imaging transducer to properly position the headset on a head. A tightening mechanism is provided to ensure acoustic coupling. Optionally, the apparatus determines whether each transducer of the headset is acoustically coupled to the head and alerts the user if repositioning is needed. 3. Transcranial ultrasound would be expected to require skilled operators and extensive control surfaces to adjust and monitor insonation. Contrastingly, in an apparatus of the invention, all functions (except an on-off/pause switch) operate autonomously so that insonation may be administered by technicians and first responders without special training, or may be self-administered intermittently as needed, prophylactically, without requirement for physician intervention or oversight. Autonomous, operator-independent operation improves consistency and reliability. Testing with the apparatus has also demonstrated safety over extended periods of use. Since the apparatus of the invention do not require diagnostic ultrasound imaging capability, there is no need for higher intensity beams to be directed against or with the direction of blood flow in the vessels of the Circle of Willis. 4. Early studies also demonstrated that appropriate selection of a pulse modulation rate was important in improving user comfort, because users with sensitive hearing may demodulate the pulse frequency and experience an uncomfortable auditory sensation. 5. By combining the self-positioning features with autonomous administration of an ultrasonic pulse train in a preset pattern or patterns that conforms to safe limits as experimentally established, the device can be used prior to obtaining a diagnosis with little or no risk, thus gaining valuable time where stroke is suspected.

Furthermore, the device is non-invasive and poses no increased risk for use where a differential diagnosis is not established. The device thus is an alternative approach that avoids one of the most difficult of the problems in stroke management, the inability to begin invasive administration of r-tPA until a diagnosis is in hand because of otherwise unacceptable risks. The evidence of risks can be readily seen for example by study of the literature (Daffershoffer et al 2005 Stroke 36:1441), where individuals receiving ultrasound in combination with r-tPA experienced unacceptable complications.

6. Thus there was a need to develop a pattern or patterns of modulated ultrasonic waveforms that would be safe and could be built into operation of the device. Disclosed here are suitable parameters for a cyclical regimen of ultrasound having defined frequency, pulse repetition frequency (PRF), pulse duration, peak rarefaction pressure; beam centerline vector, and metapulse cycle repetition frequency (MCRF), where each cyclical repetition of pulse trains is a “metapulse” or “super-nudge” having a vectored and temporal distribution of individual pulse trains. 7. Problematically, variations in transducer output due to manufacturing variance can result in substantial inconsistencies in the insonation energy that is delivered transcranially. Advantageously, the transducer-to-transducer variability inherent in the manufacture of piezoelectric crystals is compensated by digitally varying boost voltage applied to each transducer individually according to calibration data stored with the apparatus. This general approach is intended for use on a transducer-by-transducer basis, thus contributing to more reliable and consistent outcomes. 8. Headsets of the invention are configured with a built-in safe operating window for hands-free, operator-independent use, and may be operated by unskilled persons (and thus permit self-administration of ultrasound). In one embodiment, the remote control unit is supplied with only an on-off/pause switch and a status indicator. The power supply is lightweight, typically less than 1 kg, and the entire controller assembly is pocket sized and is attached to the headset by a flexible cable, thus reducing the weight worn on the head to under 500 grams so that the user may be ambulatory during operation of the apparatus or may be transported without strain or discomfort.

In addressing these problems, one embodiment of the invention is an apparatus for autonomous operation in a non-invasive, transcranial ultrasound mode, the apparatus comprising an electronic circuit with microcontroller, clock, memory, instruction set, a portable power and voltage supply, and an on/off control, where the circuit is configured for actuating a headset on which are disposed a plurality of ultrasonic transducer arrays, for example disposed circumcranially, each array having a plurality of non-focused ultrasonic transducers externally disposed on the skull and acoustically coupled thereto; and transcranial ultrasonic emissions of the transducer arrays take the form of a cyclical metapulse emission, where the transducers of the plurality of arrays are non-focused and are intermittently and alternately actuated at a low duty cycle according to a programmed sequence, each transducer emitting trains of pulses when actuated, each pulse train consisting of pulses of ultrasonic waves, each pulse having a primary ultrasonic frequency f_(c) and a pulse repetition frequency and duration, whereby the skull is insonated with a stereotemporally modulated pattern of ultrasound without operator intervention and with low power consumption, the low duty cycle eliminating the need for assisted cooling.

In one realization of a first embodiment, each pulse train comprises 2 to 300 pulses of ultrasound per pulse train at a pulse repetition frequency of 4 KHz to 10 KHz, and each pulse has a pulse duration of 0.2 to 10 microseconds; and further each transducer of the plurality of arrays has a duty cycle of 0.1 to 10% per metapulse, thereby achieving low power consumption for extended autonomous portable operation.

In another realization of a first embodiment, the pulse trains are modulated with a pulse repetition frequency of about 4 KHz to about 10 KHz, more preferably about 4 KHz to about 8 KHz, and most preferably about 6 KHz, as found suitable for reducing the sensate experience of transcranial ultrasound.

In yet another realization of a first embodiment, the microcontroller, clock, memory, instruction set, portable power and voltage supply, and on/off control are formed as a pocket-sized control module within a housing, and the power and voltage supply includes a battery pack having a weight of less than 250 grams, the battery pack having a capacity of 2 to 10 Watt-hrs and the electronic circuit having a low power consumption of less than 400 mAmp-hrs at an operating voltage of 3 to 9 VDC. The apparatus is thus operable continuously for up to 12 hours and intermittently for 24 hours or more on a single charge. At a power consumption of less than about 300 mAmp-hr, the operating life may be extended from 2 hours to 12 hours at an operating voltage of 3.5±1 VDC, and a yet longer operating life by using intermittent operation, thereby permitting transport or carrying while in extended operation mode.

In another realization of a first embodiment, the circuit comprises a) at least one pulse generator circuit for driving a resonant oscillating voltage signal at a primary frequency fc; b) a step-up transformer for generating V_(p-p) at the frequency f_(c), each step-up transformer having a centertap for electronically receiving a boost voltage from a voltage regulation circuit; and c) a demultiplex circuit (DEMUX) in electronic communication with the microcontroller and the each transformer, the demultiplex circuit for gating the oscillating voltage signal via the each step-up transformer to one or more of the transducers on command of the microcontroller, thereby causing one or more of the transducers to emit a demultiplexed acoustic pulse having an analog output with an un-derated peak rarefaction pressure P_(r0).

Electrical subcircuits may also be selected from a) a subcircuit for testing a phase angle of the demultiplexed acoustic pulse, and for signaling to the microcontroller if the phase angle is greater than a preset threshold value (indicating an uncoupled transducer); or b) a voltage regulation subcircuit with digital resistor feedback means and non-volatile data storage means for adjusting the boost voltage according to calibration data stored in memory, thereby compensating for manufacturing-related transducer-to-transducer variability.

According to one aspect of the invention, we have shown that pulse emissions driven by a voltage (V_(p-p)) configured to deliver an attenuated peak rarefaction pressure P_(rA) at depth z_(sp) not to exceed 300 KPa and not to exceed a physiologically compatible thermal index are useful and safe, overcoming a technical hurdle encountered in the prior art.

In another embodiment, the invention includes an apparatus for non-invasive therapeutic application of transcranial ultrasound, which comprises: a) an adjustably tightenable circumcranial headset assembly configured with registration surfaces for engaging at least three external craniological landmarks of a skull so as to stereotactically position the headset assembly on the skull with respect to an intracranial target or targets; b) a plurality of transducer arrays, each transducer array comprising a plurality of non-focused ultrasound transducers, where the transducers are mounted on the headset so as to be stereotactically directed at the target or targets without need for diagnostic imaging guidance; and c) operatively attached to the headset, an electronic circuit with microcontroller, clock, memory, instruction set, a portable power and voltage supply, and on/off control for actuating the plurality of transducers in a repeating cycle, each cycle a metapulse comprising a plurality of trains of pulses, each train of pulses emitted intermittently and alternately at low duty cycle from selected transducers in a programmed sequence, whereby the skull is insonated with a stereotemporally modulated pattern of ultrasound without operator intervention and with low power consumption, the low duty cycle eliminating the need for assisted cooling.

In a preferred embodiment, the at least three external craniological landmarks are nasion, Rt otobasion superius, and Lt otobasion superius, the craniological landmarks forming an Isosceles triangle which defines a foundational reference plane containing the sphenoid shelf and the Circle of Willis of the skull, the triangle having a base, an apex, and a midline, the triangle and reference plane for stereotactically positioning the headset and for stereotactically aligning the non-focused ultrasound transducers to insonate the vasculature of the Circle of Willis, the branches and junctions of the internal carotid and basilar arteries conjoined thereto, and the cerebral arteries projecting therefrom, thereby directing the insonation to the vasculature without need for diagnostic imaging guidance; and further where the plurality of transducer arrays comprise arrays selected from i) a right temporal transducer array and a left temporal transducer array or ii) a right temporal transducer array, a left temporal array, and an occipital transducer array, and where each transducer of the plurality of transducer arrays is independently controllable.

In a yet more preferred embodiment, the headset assembly may comprise a) an anterior headframe member configured for spanning ear to ear across the brow of the skull; the anterior headframe member generally “U-shaped” in form, with a first end and a second end contralaterally disposed thereon; b) a posterior headband member configured for spanning ear to ear under the occipital protuberance of the skull, the posterior headband having two ends, where each the end is configured for inserted into one apposing end of the anterior headframe member, the anterior headframe member further comprising a tensioning mechanism for engaging the ends of the posterior headband member and tightening the headset circumcranially around the skull; and c) a nasion registration bracket or brace disposed anteriorly at a midpoint on the anterior headframe member and a nasion registration pad pendant therefrom, the nasion registration pad for engaging the nasion craniological landmark and offsetting the midpoint of the anterior headframe member by a height h₁; d) a pair of otobasion superius registration members slideably disposed contralaterally on the anterior headframe member, each otobasion superius registration member with a registration surface configured for engaging one each of the Rt otobasion superius craniological landmark and the Lt otobasion superius craniological landmark; and further where the headset is obliquely inclined relative to the foundational reference plane by the height h₁ anteriorly so that the anterior headframe member is raised above the eyes of the head, has clearance around the ears of the head, and where the posterior headband member is obliquely inclined below the reference plane by a height h₂, thereby engaging the underside of the occipital protuberance of the skull when stereotactically positioned thereon.

In one embodiment, each registration surface of the otobasion superius registration member is an earpiece, and the Rt earpiece is fixedly mounted in relation to the Rt temporal transducer array and the Lt earpiece is fixedly mounted in relation to the Lt temporal transducer array, the earpieces each having dimensions for stereotactically positioning each temporal transducer array in acoustic contact with a temporal acoustic window when the nasion registration pad is seated on the nasion and each earpiece is seated on one the otobasion superius, thus forming a tripod defining the foundational reference plane. A simple embodiment is thus a stereotactic registration system where the headset rests on the ears and nose in the manner of a pair of eyeglasses.

In selected embodiments, the posterior headband may include an occipital transducer array, the occipital transducer array disposed on the posterior headband to as to be proximate to the occipital acoustic window under the occipital prominence when the posterior headband is circumcranially tightened around the skull. Advantageously, the apparatus can thus be installed by persons with little skill or training.

The apparatus of the invention finds use in non-invasively reversing, controlling or preventing ischemic stroke of the cerebral vasculature; in non-invasively reversing, controlling or preventing atheroma of the cerebral vasculature; in non-invasively reversing, controlling or preventing headache, migraine, or hydrocephaly; in combination with recombinant tPA in treatment of stroke; in non-invasively dispersing or generating an endogenous mediator of a physiological state; and surprisingly may be used non-invasively outside a 3 hour window post onset of stroke. Surprisingly, the apparatus is also effective when used for migraine.

More generally, the apparatus of the invention functions as an automaton, without the need for operator invention once emplaced on a head of a wearer and actuated. The apparatus may thus be used for self-administered transcranial ultrasound. These and other aspects of the invention are described and illustrated in more detail below.

BRIEF DESCRIPTION OF THE DRAWINGS

The teachings of the present invention can be readily understood by considering the following detailed description in conjunction with the accompanying drawings, in which:

FIG. 1 is a mechanical drawing of a fully assembled device, including headset, cable or “umbilicus”, and remote control with power supply unit in a pocket-sized housing.

FIG. 2 is a perspective view of the contents of a remote control unit with housing, indicating generally a PCB with microcontroller and associated circuitry and a battery pack power supply; here three AAA batteries. Also shown is an on-off/pause switch.

FIGS. 3A and 3B depict a mechanical headset in side and plan views.

FIG. 4 is a view of the headset on a user.

FIG. 5A is a rendering of a head with selected craniological landmarks of the skull that have a spatial relationship with the sphenoid shelf (and anterior clinoid processes) on which sits the Circle of Willis. Three such landmarks are used to stereotactically align the arrays with acoustic windows and cerebral vasculature; inset FIG. 5B illustrates the triangular foundational plane (135) of registration landmarks used for orienting the headset so that the transducer arrays are positioned and aligned in registration with the cerebral vasculature. FIG. 5C illustrates a fixed inclination of the headset relative to the foundational registration plane.

Landmarks for positioning a headset may be selected from nasion, Lt otobasion superius (LtOBS), Rt otobasion superius (RtOBS), tragion, mandibular condyle, zygomatic arch, prosthion, or occipital prominence, while not limited thereto. At least three are selected to define a triangle. As a matter of convenient field use by untrained operators, the nasion/LtOBS/RtOBS triad has proven well suited. Mounting assemblies on the headset are configured with surfaces for engaging the landmarks of the head and stereotactically orienting the transducer arrays with respect to temporal and occipital acoustic windows into the cerebral arteries of said cranium so that the device may be used without further adjustment that would require an imaging modality such as transcranial Doppler, which is not readily available to first responders, for example.

FIG. 6A is an exposed view of the cranial bones forming the sphenoid shelf and of the associated cerebral arteries. FIGS. 6B and 6C are views of the major cerebral arteries (superior and lateral views respectively) and the Circle of Willis, which can be seen resting tangential to the anterior and posterior clinoid processes and projecting in plane from the shelf or ledge formed by the greater and lesser wings of the sphenoid bone, an anatomical feature termed herein the “sphenoid shelf”, which forms the base of the anterior fossae and overlies and is generally co-planar with the orbital tracts.

FIG. 7A shows an internal view of the headset with nasion registration bracket and pad for aligning the transducer arrays with the nasion and sphenoid shelf.

FIGS. 7B and C are external views of the temporal transducer array subassemblies.

FIG. 7D is a cutaway view showing detailed structure of the temporal transducer array and housing.

FIG. 8A depicts a temporal transducer array as it interfaces with the temporal acoustic window on the ipsilateral side of the skull, as seen in an exposed view of the transducer arrays and central cerebral vasculature.

FIG. 8B is a cross-sectional exposed view showing how ultrasound beams of the temporal transducer array are directed at the cerebral vasculature. The cone is shown for purposes of representation and is not intended as a literal depiction of an acoustic wavefront emanating from a transducer.

FIG. 9A depicts a superior view of the headset assembly, showing multiple temporal and occipital ultrasound beams figuratively as superimposed on the cerebral vasculature.

FIG. 9B is a cutaway view showing how ultrasound beams of the occipital transducer array are directed at the cerebral vasculature.

FIG. 10A is a block diagram of an energy efficient circuit (300) for patterned ultrasonic insonation with adjustable amplitude.

FIG. 10B is a schematic showing transducer voltage regulation circuitry (310) at the component level.

FIG. 10C is a schematic view of a simplified ultrasonic pulse generator circuit (320) with a receive circuit.

FIG. 10D illustrates multiplexed operation for sending and receiving signals to and from a transducer array.

FIG. 11A illustrates a “pulse” consisting of about 12 sinusoidal sound waves. FIG. 11B illustrates a pulse train consisting of 20 pulses. FIG. 11C illustrates a pair of pulse trains, each pulse train consisting of multiple pulses in series.

FIG. 12A is an example of a metapulse cycle involving sixteen ultrasonic transducers. Combining the traces, the figure represents a pattern of asynchronous ultrasonic pulse train emissions (i.e., a “metapulse cycle”), where each single crystal is directed at a distinct anatomical target and is fired once per cycle.

FIG. 12B is a second example of a metapulse cycle, here having duplex, paired transducer firings.

FIG. 12C is a third example of a metapulse insonation cycle, here having triplex simultaneous transducer firings.

FIG. 13 quantifies the audible sensation of ultrasound exposure as a function of modulated pulse train frequency.

FIG. 14A is a plot of voltage (V_(p-p)) versus I_(sppa.0) (W/cm₂), showing transducer output under tank conditions.

FIG. 14B is a plot of voltage (V_(p-p)) versus peak rarefaction pressure (P_(r)) at a z_(sp) characteristic of the transducer in situ; several frequencies are shown.

FIG. 15 is a flow diagram (350) for operating the apparatus with calibration-adjusted “on the fly” voltage regulation specific for each transducer.

FIG. 16A illustrates peak rarefaction pressure (P_(r)) as a function of depth for selected increments in transducer voltage (V_(p-p)).

FIG. 16B plots the relationship between peak rarefaction pressure and ICH conversion (%) as determined here from analysis of data from clinical trials.

FIG. 17A is a plot of peak rarefaction pressure illustrating the effect of thick and thin skull phenotype on peak rarefaction pressure as a function of depth at 1 MHz.

FIG. 17B is a curve fit for attenuation coefficient (A_(TempBONE)) versus frequency for temporal bone.

FIGS. 18A and 18B are renderings of physical models for analysis of attenuation profile as a function of depth for a trans-temporal transducer (FIG. 18A) and for a transducer apposing a non-boney, sub-occipital acoustic window (FIG. 18B).

FIG. 19 is a logic diagram (390) for automated operation of an apparatus where emission voltage is adjusted to detect acoustic coupling each transducer.

FIGS. 20A and B describe the use of phase angle to verify acoustic coupling. FIG. 20B plots voltage output corresponding to phase angle for a coupling verification circuit of FIG. 21.

FIG. 21 illustrates schematically a coupling verification circuit (400) which relies on a voltage comparator having the output of FIG. 20B.

FIG. 22 depicts schematically the competing cycle of fibrinogenesis (coagulation) and fibrinolysis (thrombolysis).

FIG. 23 is a schematic of the major limbs of the classical coagulation model.

FIG. 24 is a schematic of the “cellular model” of coagulation (after Monroe 2001 Thromb Haemost 85:958-965).

FIG. 25 depicts fibrinolysis involving endogenous tissue plasminogen activator (e-tPA) and ultrasound.

FIGS. 26A and 26B depict a model for vascular vasodilation with release of endogenous nitric oxide, where blood shear (FIG. 26A) is replaced by noninvasive ultrasound from an apparatus of the invention (FIG. 26B).

NOTATION AND NOMENCLATURE

Certain terms throughout the following description and claims are used to refer to particular features, steps or components. As one skilled in the art will appreciate, different persons may refer to the same feature, step or component by different names. This document does not intend to distinguish between components, steps or features that differ in name but not in function or action. The drawing figures are not necessarily to scale. Certain features or components herein may be shown in somewhat schematic form and some details of conventional elements may not be shown in the interest of clarity and conciseness.

Certain meanings are defined here as intended by the inventors, i.e. they are intrinsic meanings Other words and phrases used here take their meaning as consistent with usage as would be apparent to one skilled in the relevant arts.

Acoustic Pulse—a series of sinusoidal ultrasonic pressure waves (209) forming a pulse (210), the pulse having a frequency and a pulse duration, where downfield acoustic pressure is seen to rise to a plateau as the number of pressure waves approaches fifteen.

Pulse Train—a series of pulses of emitted ultrasound, also termed an “acoustic nudge”, each pulse train (211) having an ultrasonic frequency, a pulse number or count, a pulse duration, a pulse repetition frequency (PRF) and a beam centerline vector.

Acoustic “Metapulse”—a series of pulse trains of emitted ultrasound, also termed a “acoustic super-nudge”. In one embodiment the pulse trains of the metapulse (212, 214, 216, 218) may be directed from spatially distributed ultrasound transducers of a plurality of transducer arrays. A “metapulse” is composed of multiple “nudges,” each nudge a train of pulses, each pulse a burst of waves, and is cyclically repeated in an insonation regimen. Each “metapulse” has a metapulse cycle repetition frequency (MCRF).

Pulse repetition frequency (PRF)—for a pulsed waveform, is the number of pulses generated per second in a pulse train, typically cited as Hz or KHz.

Metapulse cycle repetition frequency (MCRF)—the frequency at which complete pulse cycles are emitted from a headset, each headset having a plurality of transducers, each firing independently and in isolation in a predetermined sequence, typically given in units of Hz.

Pulse Duration (PD)—the time of duration of a pulse, also termed the pulse width, and may be expressed in units of time or as a number of cycles at a frequency.

Pulse Interval (PI)—the time between consecutive pulses, which is commonly estimated as the inverse of the pulse repetition frequency.

Duty Cycle—in pulsed ultrasound, refers to the ratio of pulse duration to pulse interval (DC=PD/PI).

Waveform—the graphical characterization of an acoustic wave, showing time on an x-axis and pressure or intensity on a y-axis. As used herein, also refers to a more complex pattern in which ultrasonic waves emitted by a plurality of arrays, each array having a plurality of transducers, are temporally and spatially modulated.

Peak Rarefaction Pressure (P_(r))—The peak rarefactional pressure P_(r) is the absolute value |P_(r)| of the half amplitude of a sound pressure wave passing through tissue. Compression is the increase in pressure and rarefaction is the reduction in pressure of the medium during the acoustic wave cycle. Peak rarefaction pressure may be derated for losses to scattering and absorption when travelling through homogeneous and inhomogeneous matter. Peak rarefaction pressure for air-backed transducers may deviate slightly from nominal due to the effect of ringdown.

Mechanical Index (MI)—The mechanical index is an indicator of the likelihood of non-thermal bioeffects (such as cavitation). The mechanical index is defined as the peak rarefactional pressure (derated peak pressure at negative amplitude) divided by the square root of the ultrasound frequency. MI=P _(r0.3) /√{square root over (f)}

As the mechanical index increases, the likelihood of bioeffects within tissue increases.

Regulatory limits generally allow a mechanical index of up to 1.9 to be used for most tissues except opthalmic. At low acoustic power, the acoustic response is generally linear.

Intensity, spatial-peak temporal average (I_(spta))—The value of the temporal average intensity at the point in the acoustic field where the intensity is at a maximum; measured in Watts/cm². I_(spta.0) is a complex function of the voltage applied to the transducer and the piezoelectric, magnetostrictive, or electrocapacitive effect on the transducer. I _(spta.0)=(ρc ⁻¹)*∫₀ ^(PD) P _(r) ²(t)/dt

Thermal Index (TI)—is a calculated estimate of temperature increase with tissue absorption of ultrasound and is determined by the ratio of the total acoustic power to the acoustic power required to raise the tissue temperature by 1° C. Some devices further subcategorize the TI according to the insonated tissue: soft tissue thermal index (TIS) for soft homogeneous tissues, cranial bone thermal index (TIC) for bone at or near the surface, and bone thermal index (TIB) for bone after the beam has passed through soft tissue. More generally, the temperature of insonated tissue increases with increasing intensity and with increasing frequency.

Non-focused transducer—refers to a transducer producing a divergent beam exiting the near field, where beam diameter progressively increases with depth in the far field. The near field length and hence the natural divergence of an ultrasonic beam are determined by aperture (equal to element diameter in the case of conventional monolithic transducers) and wavelength (wave velocity divided by frequency). For an unfocused transducer, the near field length, beam spread angle, and beam diameter can be calculated as follows: L=D ² f _(c)/4c where, L is near field length, D is element diameter or aperture, f_(c) is the frequency, and c is the sound velocity in the medium.

Focused transducer—within its near field, a transducer can be focused to create a beam that converges rather than diverges. Narrowing the beam diameter to a focal point increases sound energy per unit area within the focal zone and thus has found use in therapeutic applications (Cintas 2002). Conventional piezoelectric slab transducers usually do this with a refractive acoustic lens, while phased arrays do it electronically by means of phased pulsing and the resulting beam shaping effects.

Phased Array—a composite transducer having physically contiguous sub-elements where the sub-elements are electronically controlled for independent actuation.

Automaton: refers to an apparatus or device that autonomously performs certain actions, here patterned emissions of ultrasound from a headset worn over the head, by executing preset controls or encoded instructions without human intervention, and is thus operable, after activation, in “hands-free” mode such that operator-independent insonation is performed. The device may include an electronic control circuit equipped with a microcontroller, non-volatile memory for storing instructions and reference data, clock functionality for generating ultrasonic pulses and for actuating individual transducers according to a timed sequence, and afferent and efferent connections for receiving and transmitting commands and signals to and from peripheral devices such as transducers, acoustic coupling circuitry, and an associated receiving and wireless transmission circuitry, for example. The apparatus as defined herein is non-invasive and lacks a surgical component in a method of use. In a preferred embodiment, the automaton is operated according one or more regimens and look-up tables that define the ultrasonic waveforms of a metapulse cycle and the amplitudes to be generated by the device.

Stereotactic positioning—A method in neuroscience for locating points within the brain using an external frame of reference; as used here, relating to positioning with respect to a tissue, esp. in the brain. We have established a preferred frame of reference for sonothrombolysis using external osteology, where the cranial frame of reference is based on one or more craniological landmarks of the head selected from nasion, Lt otobasion superius, Rt otobasion superius, tragion, mandibular condyle, zygomatic arch, prosthion, and/or occipital protuberance, and most preferably a triangular frame of reference based on the nasion, and the Rt and Lt otobasion superiora landmarks, which establish the relative positions of the temporal and sub-occipital acoustic windows, the sphenoid “shelf” formed by the greater and lesser wings of the sphenoid bone, the anterior and posterior clinoid processes, dorsum sellae, and the Circle of Willis with cerebral arterial circle, bifurcations of the internal carotid artery conjoining the anterior, middle and posterior cerebral arteries, and junctures of the basilar artery with the communicating cerebral arteries and the vertebral arteries. This frame of reference has proved more robust in practice than Broca's reference plane, also termed the “neuro-ocular plane” (NOP) as used by radiologists, although the two reference planes are relatively closely aligned, and is much preferred over the Frankfurt-Virchow plane, which lies oblique to and below the target anatomy. While the NOP, which follows the orbital tracts, is slightly below and parallel to the Circle of Willis, its use requires a measurement of 3.3 cm above the tragion, and hence is not readily practiced by unskilled persons. In contrast, the reference plane established herein is readily practiced without instruction using a first embodiment of the headset of the invention. Heights above and below the foundational reference plane used here are preset by the headset geometry and transducers are angled accordingly so as to insonate an intracranial target or targets of interest.

Streaming—an effect of ultrasound on the behavior of insonated liquids. Mechanisms whereby low-intensity ultrasound increases enzymatic fibrinolysis include acoustic streaming at clot/blood flow boundary and reversible changes in fibrin structure, which both result in increased plasminogen activator binding to fibrin and transport into the clot. Acoustic streaming associated with harmonic oscillation of microbubbles has also been termed microstreaming. Acoustic streaming and microstreaming also promotes flow of interstitial and blood fluids, as described for example by Eggleton and Fry (U.S. Pat. No. 3,961,140).

Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment of the present invention. Thus, the appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, particular features, structures, or characteristics of the various embodiments of invention may be combined in any suitable manner in one or more embodiments.

Conventional—refers to a term or method designating that which is known and commonly understood in the technology to which this invention relates.

Unless the context requires otherwise, throughout the specification and claims which follow, the word “comprise” and variations thereof, such as, “comprises” and “comprising” are to be construed in an open, inclusive sense, that is as “including, but not limited to”.

The appended claims are not to be interpreted as including means-plus-function limitations, unless such a limitation is explicitly recited in a given claim using the phrase “means for.”

DETAILED DESCRIPTION

Although the following detailed description contains many specific details for the purposes of illustration, one of skill in the art will appreciate that many variations and alterations to the following details are within the scope of the invention. Accordingly, the exemplary embodiments of the invention described below are set forth without any loss of generality to, and without imposing limitations upon, the claimed invention.

FIG. 1 is a drawing of a fully assembled apparatus (100), including headset (101), cable or umbilicus 103, and remote control with power supply unit in a pocket-sized housing 102. The remote control is supplied with an on/off or pause actuator or button (107) and a status indicator bar (108). The headset is designed for extended periods of wear and weighs less than 500 grams; the overall apparatus weighing less than 1 kg. As configured here, three transducer arrays are mounted in the circumcranial headset and each tranducer array contains a plurality of crystals, each about 1 cm in diameter. In a first embodiment of the invention, a device having 16 transducers was built, 6 transducers each per temporal array (105 a, 105 b) and 4 transducers per occipital array (106). Each transducer is a piezoelectric crystal designed to operate at a particular frequency. Systems operated at 1 MHz and at 2 MHz have been built and tested. Systems having 12 or 20 transducers, and operated at one or more base or “primary” frequencies selected from a range of 500 to 3500 KHz are also contemplated, for example.

Transducers emit ultrasound in pulses, the pulses in trains of pulses, the trains of pulses modulated in time and position. Advantageously and paradoxically, this reduces insonation intensity and power draw—but increases effectiveness. In order to reproducibly orient the headset without use of an imaging study, the apparatus is fitted to selected craniological landmarks of the skull, shown here is a nasion registration brace with pad or nosepiece (104) which will be described in more detail below.

The structural shell or supporting members of the headset assembly may be constructed of plastic, the plastic a generally radiolucent material having a low Hounsfield density. Plastics include polycarbonate, acrylonitrile butadiene styrene (ABS), styrene-acrylonitrile, polystyrene, nylons, polyethylenes, acrylates, and so forth. For example, Bayblend (Bayer MaterialScience, Dusseldorf DE) may be used in construction of headsets of the invention, although not limited thereto. The CT translucency of various plastics has been described by Henrikson (1987, CT evaluation of plastic intraocular foreign bodies, Am J Neuroradiology 8:378-79).

FIG. 2 is a perspective view of the contents of the remote control unit (102) with housing case (112) and cover (111), figuratively showing a printed circuit board (116) with microcontroller (115) and generalized associated circuitry. Also shown, mounted in the cover, is a battery pack power supply (113); here three AAA batteries (114). Also shown is an on-off/pause switch (107) and at least one status indicator (108) such as an LED, or other status indicator such as a buzzer or a liquid crystal display.

The printed circuit board is supplied with leads to a junction (117) that forms a power and data bus routed through umbilicus 103 to the headset 100.

The battery pack may be selected from a number of compact batteries commercially available that can deliver about 200 mAmp-hrs, 400 mAmp-hrs if needed, without recharging for up to about 12 hours at an operating voltage of about 1.5 to about 4 VDC, most preferably about 3.5±1 VDC, but optionally about 9-12 VDC. The battery pack will thus have a capacity of 0.6 to 15 Watt-hours and preferably has a weight of less than 250 grams, more preferably less than about 100 grams, and most preferably less than about 50 grams. The battery may be generically a rechargeable battery, an insertable battery, a lithium ion battery, a lithium ion polymer battery, a lithium iron phosphate battery, a lithium-sulfur battery, a lithium-titanate battery, a nickel-zinc battery, a nickel-iron battery, a NiCd battery, a NIMH battery, an alkaline battery, a 9 V battery, a cell phone battery, or at least one AA or AAA battery (114, as shown), and so forth.

The battery pack is rechargeable or replaceable, and optionally where rechargeable, may include a control circuit with “fuel gauge” circuit such as is available from Benchmark (BQ2040) for use in recharging the battery pack. Cell phone batteries are typically about 3.7 V and can deliver about 1 Amp-hr or about a specific power of 20 to 40 mAmp-hrs/gm or more. For example, an apparatus of the invention having a maximal power draw of 400 mAmp-hrs that is operated for 2 hrs in continuous mode and subsequently for 10 hrs in intermittent mode at 200 mAmp-hrs will require a battery pack of about 2.8 Amp-hrs capacity. An apparatus having a maximal power draw of 200 mAmp-hrs would require only 400 mAmp-hrs for operation over a 2 hr cycle, and hence could be operated with three AAA batteries in series supplying about 4 volts. New batteries could be installed if needed and the total weight of the battery pack is 50 gm or less, by way of example. Advantageously, this permits portable, extended operation, such as for ambulatory transcranial ultrasound.

FIGS. 3A and 3B depict a headset assembly (101) from side and superior views. The inventive devices are built with multiple transducers (here shown clustered in two paired contralateral temporal transducer arrays 105 a, 105 b and a posterior occipital transducer array 106, each transducer array having a plurality of individually powered piezoelectric crystals) and a stereotactic registration or positioning system having nose and ear registration brackets for aligning the transducers with the corresponding acoustic windows and cerebral vasculature. External landmarks are used to position the arrays with respect to internal vascular targets in the brain, solving a problem that would otherwise potentially delay initiation of insonation. While the transducers selected for this device are non-focussed, the beams have a center axis and a width of maximal acoustic pressure, so for both efficacy and safety reasons, orientation of the beams stereotactically with respect to brain anatomy is preferred. At least three registration surfaces are used in conjunction for stereotactically positioning the headset assembly on a head of a wearer. A first registration bracket (120) is shown mounted anteriorly inside the headframe.

Many strokes are found to be strokes of the cerebral arteries associated with the circle of Willis. Thus locating the Circle of Willis with respect to external craniological landmarks proved a useful solution to the question of orienting the transducers without need for reliance on imaging studies by a skilled sonographer or radiologist.

The headset of the figure is constructed of an arcuate anterior headframe member (101 a) for fitting to the front of the head and an arcuate, pliant, posterior headband member (101 b) that is adjustable by means of a tightening mechanism or knob (119) within the body of the anterior headframe member, into which opposite ends of the posterior headband insert. Tightening is achieved by tensioning the posterior headband member and does not affect placement of the anterior headframe member with registration brackets, thus ensuring that the stereotactic alignment with respect to the cerebral vasculature is not disturbed.

FIG. 4 is a view of the headset on a user. The cable (103) is optionally detachable so that the headset is optionally disposable. Alternatively, the cable may be integrated into the headset and be detachable from the housing for the power supply and electronic controller.

The nasion registration brace (120′) is part of the nasion registration bracket (120) and supports a nosepad (104) adapted to be fitted against the nasion on the bridge of the nose of the user. As will be shown, this is one of three registration elements used to orient the headframe with respect to transcranial acoustic windows and target vasculature.

FIG. 5A is a rendering of a head with characteristic external craniological landmarks of the head that have a spatial relationship with the sphenoid shelf (marked by the anterior clinoid processes, see FIG. 6A) on which sits the major aspect of the Circle of Willis which is at the center of the cerebrovascular tree or nexus. Three such landmarks are used to stereotactically align the arrays with acoustic windows and cerebral vasculature; FIG. 5B illustrates a triangular plane of registration landmarks which used for orienting the headset so that the transducer arrays are positioned and aligned in registration with the cerebral vasculature. The triangle is an Isosceles triangle and has a base and is bisected by a midline that runs anteriorposteriorly through the cranial vault generally tangentially to the sphenoid shelf and parallel to and slightly above the optical tract. The reference plane described by the triangle is an external guide to the location of the cerebral vasculature most susceptible to stroke. The triangle is bisected by a midline (136) which defines the cerebral hemispheres.

Landmarks for positioning a headset may be selected from nasion (130), otobasion superior, OBS, 131), tragion (132), auditory meatus (auricular point, 133), mandibular condyle, zygomatic arch, prosthion, bregma (134), or occipital prominence (OCP). At least three are selected. The mechanical brackets are configured with surfaces for engaging the selected landmarks of the head and stereotactically orienting the transducer arrays with respect to acoustic windows onto the cerebral arterial tree of the brain.

In a preferred embodiment, the nasion, and left and right OBS are chosen as shown. The Alleman Plane (135) is defined by an Isosceles triangle having a base formed by a line connecting the right and left otobasion superius (OBS, 131 a, 131 b) and lines joining with an apex of the triangle at the nasion (130). This triangle rests on the Alleman Plane. FIG. 5C shows that the headset may be inclined from the Alleman Plane by offsetting the anterior headframe member by a height “h₁” above the nasion. Height h₁ is generally taken as about 2 centimeters. In this way the anterior aspect of the headset clears the brow of the wearer; literature citations indicate that the adult height of the glabella is 0.7 to 1.6 centimeters above the nasion. The posterior headband member is seated below the occipital protuberance by a height h₂. When so inclined, the headset continues to rest on the OBS registration landmarks but is now tilted as shown (“headset inclination”, 138). The headset is inclined from the reference plane by height h₁, the inclination angle “theta” is generally taken as about or approaching 12 degrees. The temporal transducer arrays may then be slideably positioned on the headframe over the temporal acoustic window (137). Individual temporal transducers are angled superiorly and anteriorly (see FIG. 7D) to target various aspects of the cerebral arterial tree. Approximate locations of the tragion (132) and the auditory meatus (with center auricular point, 133) are shown for reference.

FIG. 6A is an exposed view of the cranium (140) showing the cranial vault (141) and bones forming the sphenoid shelf (143) and the general position of the major cerebral arteries (142, 144). FIGS. 6B and 6C are views of the major cerebral arteries (superior and lateral views respectively) and the Circle of Willis (144), herein also termed the cerebral arterial nexus, which can be seen resting partially in FIG. 6A on the shelf or ledge formed by the greater and lesser wings of the sphenoid bone, an anatomical feature termed herein the “sphenoid shelf” (143), which forms the base of the anterior fossae overlying the orbital tracts and is generally co-localized with the Alleman Plane.

Shown are the anterior cerebral artery (ACA), middle cerebral artery (MCA), posterior cerebral artery (PCA), internal carotid artery (ICA), basilar artery (BAS) and vertebral arteries (VER) and their connections to the Circle of Willis (144).

FIG. 7A shows an elevation view of the nasion registration bracket (120) for aligning the transducer arrays with the nasion and sphenoid shelf (in conjuction with the OBS registration brackets described below). The nasion registration brace (120′, vertical element with height h₁) includes a beveled wedge or nosepiece (104) for positioning against the nasion under the glabella and is rigidly attached to the anterior headframe member (101 a) of the headset assembly. The headframe also contains a tightening knob (119) that operates by a ratcheting mechanism on the right and left ends of the posterior headband member (101 b, see FIG. 3B).

Also shown is an end view of the two ends of the anterior headframe member, detailing the structure of an adjustment slider track (152) for slideably repositioning the temporal transducer array assemblies (FIGS. 7B-7D). Also shown is receiving orifice for the cable junction (151) and the insertion slot (150) for insertion of the posterior headband assembly.

A temporal transducer array subassembly (105 b) is now described in more detail. FIGS. 7B and C are external views showing the lateral OBS registration brackets (or earpiece, 154) with surface adapted for aligning the temporal transducer arrays with the otobasion superius (OBS) and sphenoid shelf. Also shown is a slider foot (153) that inserts into the slider track (152) of the headframe and permits fitted positioning the transducer arrays anterior to the ear of the wearer so that the transducer array engages temporal acoustic window 137. FIG. 7D shows a cross-section through a piezoelectric crystal of the temporal array and illustrates the slider that mounts in the adjustment slider track shown in FIG. 7A.

It can be seen that the Rt temporal transducer array and OBS registration bracket with registration surface for engaging the Rt otobasion superius are rigidly affixed to a Rt temporal subassembly, said Rt temporal subassembly being slideably mounted to the headset assembly on a track (152, right) for anterioposterior adjustment in relation to the midline; correspondingly the Lt temporal transducer array and the Lt OBS registration bracket with registration surface for engaging the Lt otobasion superius are rigidly affixed to a Lt temporal subassembly, the Lt temporal subassembly being slideably mounted to the headset assembly on a track (152, left) for anterioposterior adjustment in relation to the midline and base of the triangle.

As can be seen in FIG. 7D, the transducers are optionally enclosed in a housing (marked here on lower aspect 156 a) with baseplate 156 b shown here in cross-section. Transducers (155 a) forming a hexapartite array are show. Transducers 155 b and 155 c are shown in cross-section. A profile view of the slider foot 153 is also shown here. The housing includes a thin overlayer 157 as a coupling layer for more efficiently coupling acoustic output to the skull. This overlayer may be a polyurethane, a polyethylene, a silicon, a rubber, and so forth, having a relatively soft and compliant modulus intermediate between the hardness of the transducer and the hardness of the skull or couplant gel. Other means for improving coupling are described by Horzewski and others and are incorporated by reference here. Couplant gels are well known in the art.

When properly positioned on the wearer, the lower aspect of the temporal transducer arrays 156 a are generally aligned with and above the upper border of the zygomatic arch so that the transducers 155 are firmly engaged and acoustically coupled with gel against the temporal acoustic window.

In one embodiment of the invention, the several transducer assemblies (105 a, 105 b, 106) are configured to be detachable so as to be saleable as a kit, where the kit consists of a transducer array in a disposable module prefitted with a “ready-to-use” gel couplant pad in a sealed packet. A mounting receptacle is provided which is pre-attached to the anterior headframe assembly 101 a and the transducer arrays themselves are removed from their sealed packets and snapped into place in the corresponding mated receptacle on the headframe prior to use. The transducer modules are provided with wiring pins that are plugged into a female socket in the mounting receptacle and the apparatus performs a functional self-check using integrated watchdog circuitry before beginning insonation. In this way, the required gel couplant is provided with the apparatus. Optionally, the apparatus may also perform a self-check to verify acoustic coupling, such as by use of the phase comparator circuitry described later in this description, prior to initiation of cyclical metapulse emission.

FIG. 8A depicts a temporal transducer array (105) as it interfaces with the temporal acoustic window on the ispilateral side of the skull, as seen from a superimposed view of the transducer arrays and central cerebral vasculature (visible are BAS and the Circle of Willis, 144). Anchoring of the occipital transducer array (106) under the OCP is also shown in this view. It can be seen that the nasion registration riser (120′) with beveled pad (104) and posterior strap (101 b) under the OCP stabilize the anatomical position of the headset when tightened by tensioning knob 119 during use. In this position, the head may be bent forward to open the occipital acoustic window without loss of stereotactic positioning of the Rt and Lt temporal transducer arrays.

FIG. 8B is a “see-through” perspective view showing figuratively how the (non-focused) ultrasound beams of the temporal transducer array are directed at the internal anatomy of the cerebral vasculature. The cone is shown for purposes of representation of the −6 dB radial boundary of each beam and is not intended as a literal depiction of an acoustic wavefront emanating from a transducer. The temporal acoustic window is chosen as one of the thinner of the boney plates surrounding the brain. Beams (160 a, 160 b) entering the temporal acoustic window from transducers 155 of the Rt temporal array (105 b) are shown to continue (161) through the major nexii of the cerebral vasculature. Marked are the MCA, ACA, ICA and Circle of Willis (144). It can be seen that by alternating emissions from the Rt and Lt temporal arrays, both hemispheres of the brain receive emissions equally in the absence of an imaging study to suggest further localization of the beams.

FIG. 9A depicts a superior view of the headset assembly (101) as would be positioned on a skull, showing temporal (cones, 160) and occipital ultrasound beams (cones, 162) figuratively targeted at a central cerebral vasculature. It can be seen that the −6 dB radial boundary effectively targets the vasculature of interest in two directions (161, 163). This stereotactical targeting of the incident beams, which are non-focused, aids in the effect of the emissions. In this embodiment, the occipital transducer array 106 contains four transducers 166.

FIG. 9B is a “see through” lateral view showing how the ultrasound beams of the occipital transducer array 106 are directed at the internal cerebral vasculature. Beams are represented by −6 dB cones (162 a, 162 b). When properly angled and positioned using the stereotactic positioning aides of the invention, transducers in the occipital array can be directed at the basilar and vertebral artery as well as the junction of the internal carotids and anterior/posterior communicating arteries of the Circle of Willis.

Referring now to FIG. 10A, shown is a block diagram of a circuit schematic (300) with functional blocks indicating the basic electronic components of a system operating as an automaton. A wiring harness from the headset is attached and is indicated here by a coaxial cable (COAX). Although multiple leads for powering multiple transducers may be contained in the wiring harness, only a single lead and transducer is shown here.

The microcontroller (301) is optionally an Intel P8051 (MCS51), but is not limited thereto. Microprocessors with advanced mathematical processing capacity may also be used. The MCS51 package may contain fully integrated non-volatile memory such as EEPROM, and RAM, IO, UART and timer functionality, or optionally the accessory functions may be discrete. Shown here as independent functionalities are an EEPROM unit (302) for providing programmable instructions and look up tables to the microcontroller, a CLOCK functionality (303) for providing a frequency that may be used by a clock divider and by the microcontroller, and four functional blocks related to transducer send and receive functions, including a multiplexer (MUX, 304), a demultiplexer (DEMUX, 305), a voltage or “boost” regulator (VREG, 306), and a pulse generator subcircuit (PULSE GEN, 307).

The pulse generator, demultiplexer and voltage regulator are used to control and direct pulsed waveforms to the transducer or transducers. The pulse generator circuit drives a resonant oscillating voltage signal at a primary frequency f_(c). The voltage regulator receives a voltage V_(BAT) from a battery (not shown) and outputs a higher voltage V_(BANG). V_(BANG) is used to control individual transducer V_(p-p), i.e. transducer insonation amplitude. The voltage regulator may be an LM4510 (Natl Semiconductor) Step-Up DC/DC Converter, while not limited thereto. The LM4510 is designed to delivery up to 120 mA at 16V from a 3.6V input of a lithium ion battery at a switching frequency of 1 MHz with greater than 85% efficiency, with provision for non-synchronous operation at light load to maximize power efficiency. NMOS output is regulated by a bias voltage applied at a feedback connection. The fixed frequency is dependent on an external LC oscillator wired to the FET transistor. No Schottky diode is required. R2 is an isolation resistor and C1 is a filter. Capacitor C2 works with transformer T1 (309) and the piezoelectric crystal TDX to resonate at a center frequency f_(c).

As described in FIG. 10B, a voltage regulatory circuit (310) for V_(BANG) is modulated by feedback resistor bias voltage (WIPER) applied to pin FB of a LM4510 Boost Regulator (311), for example. By substituting a digital potentiometer DS1804 (314, supplied by Dallas Semiconductor (Dallas Tex.), or equivalent device, for the fixed resistance customarily used, control of V_(BANG) applied to the centertap of the transformer is achieved, and transducer insonation amplitude may be increased or decreased on the fly. In this way the voltage of each pulse or burst directed to an individual transistor by the DEMUX logic gates is “dialed in” to produce a corresponding amplitude of transducer insonation at each individual transducer as necessary to compensate for transducer-to-transducer variability, an advance in the art.

V_(BANG) may be used to control for manufacturing variation in transducer output versus applied voltage. An efficiency or rating factor for each transducer crystal stored with the headset or transducer subassembly may be accessed by the microcontroller during startup and used to separately vary the voltage applied to each crystal of the headset so as to compensate for manufacturing variation. This accomplishes an advantageous reduction in intra-headset variability of ultrasonic treatment.

The microcontroller is responsible for controlling V_(BANG) via a signal (315, uC) to a digital potentiometer, which generates a WIPER voltage applied to the feedback input (FB) of the voltage regulator for controlling the voltage boost. Signal values to be applied for each transducer of an array may be stored in tables in nonvolatile memory. The non-volatile memory may be the EEPROM shown in FIG. 10A or a remote memory associated with the array subassemblies on the headset and accessed via a digital bus. Also shown by way of illustration of a working embodiment are external capacitor C3 (313) and inductor element L3 (312) used with the internal FET switch in the voltage boost functionality for boosting voltage under microcontroller control, here using the LM4510 boost regulator and digital feedback potentiometer (DS1804), while not limited thereto.

Referring again to FIG. 10A, the PULSE GEN functionality (307) generates a waveform FREQ1 corresponding to the ultrasonic resonant frequency of the transducer TDS. FREQ1 controls switch SW1 when AND gate 308 is high and drives a resonant oscillation in transformer T1 (309). FIG. 10C describes the PULSE GEN functionality at a component level (320), where transformer T1 is provided with centertap for receiving V_(BANG) and switches for driving the transformer at frequency f_(c), which in turn drives transducer 321. Switches Phi1 and Phi2 are controlled by the microprocessor and clock functions. SEL is received from DEMUX as described below.

To turn on AND gate (308, FIG. 10A), DEMUX (305) output SELX is addressed under control of the microcontroller. In one embodiment, the DEMUX function is a 4:16 demultiplexer for address decoding, where each address is one of sixteen transducers and is controlled by a separate AND gate. The DEMUX function is used to gate the FREQ1 signal through a step-up center tap transformer for generating a 0 to 250 V signal applied across each transducer crystal, which in operation behaves in certain respects as a capacitor. The transformer T1 and transducer TDX pair may be viewed as a resonant LC pair having higher power efficiency. In this way, a fixed frequency (for example 1 MHz or 2 MHz) is applied to the transducer(s) in bursts or pulses, with a pulse frequency controlled by the DEMUX signal applied to the AND gate (308). More generally, a plurality of transducers (330 a, 330 b, 330 n) are gated (331 a, 331 b, 331 n) in this way as shown in FIG. 10D and a primary frequency signal (PULSE GEN, 332) may be selected between 500 KHz to 3.5 MHz, for example. Working in conjunction with V_(BANG), the demultiplex circuit output to the transducers has an analog output with an un-derated peak rarefaction pressure P_(r0). By using a second or third pulse generator circuit gated in parallel, frequencies and intensities sent to any particular transducer of an array may be customized for particular applications. The DEMUX functionality may also address multiple transducers at once if desired for simultaneous firing in pairs or triplets. Intermittent firing of the transducer allows the headset to be operated without assisted cooling and is a low power consumption feature of the circuitry.

MUX (304, FIG. 10A) and associated circuitry (320) is used in “receive” mode to collect echo voltage generated at the transducer (TDX, 321) surface as received on the input lead and to convey a digitized voltage signal to the microcontroller, generally as shown in FIG. 10C, where the sensed voltage signal is Rcv. Like DEMUX, MUX is multiplexed to collect voltages from multiple transducer leads. Multiple transducer signals from an array or arrays of transducers may be multiplexed in this way. The coaxial cables as shown (COAX) in FIGS. 10A, B and D thus may consist of multiple bundled leads and the wire harness has corresponding multiple points of attachment to the printed circuits for performing the block functions of FIG. 10A. MUX output to the microcontroller thus is a digital signal with unique address corresponding to each transducer.

As previously alluded to, frequency, pulse repetition pattern, and pulse metacycle rate are factors in efficacy and safety and the patterned waveforms selected for use are features of the invention. Primary frequencies selected for operation of the devices of the invention are in the range of 0.5 to 3.5 MHz. As frequency is increased, mechanical index (MI) decreases, but thermal index (TI) increases inversely. Therefore a range of 0.8 or 0.9 to 3.0 MHz is a preferred range. Reduction to practice at 1 MHz and 2 MHz has been realized. Other preferred frequencies are about 1.2 MHz or 0.8 MHz. Care is taken in selecting parameters of pulse width, intensity and pulse repetition frequency not to exceed an integrated I_(spta.3) limit of about 720 mW/cm². Cyclical metapulse repetition frequency (MCRF) and duty cycle may also be used to limit power consumption and permit heat dissipation by passive means such conductive and convective cooling from external surfaces of the headset and transducers, and are configured not to overstress the cooling capacity of the wearer. Eliminating the need for active cooling dramatically decreases overall power draw of the apparatus and is an advance in the art.

FIG. 11A illustrates by way of example a typical pulse consisting of multiple sinusoidal sound waves (339) at a primary frequency f_(c). Each pulse (340) consists of about 12 sound waves as shown. At 2 MHz, a pulse of this kind has a pulse width of about 6 microseconds. Pulses of this kind may be fired in series with a pulse repetition frequency (PRF) of about 6 KHz, for example, and are thus fired from an individual transducer at a pulse interval (PI) of about 167 microseconds, corresponding to a duty cycle of about 3.6%, while not limited thereto. Duty cycle may range from 0.1-10%, more preferably 3-5%, and most preferably about 3.5±0.5%. In other embodiments, pulse amplitude modulation or pulse frequency modulation may also be used.

FIG. 11B depicts a series of about 20 pulses (340 a-340 n) emitted from a single transducer. Taken together, the individual pulses form a ‘pulse train’ (341).

FIG. 11C illustrates a pair of pulse trains (341 a, 341 b), each pulse train consisting of multiple pulses in series. Scale is not shown and the individual pulses are not distinguishable. For illustration, 100 to 300 pulses may be grouped in a single pulse train fired from a single transducer, the pulse train having a pulse repetition frequency (PRF). In this figure, two consecutive pulse trains (341 a, 341 b) are shown, a repeated cycle of consecutively fired pulse trains constitutes a “metapulse” (342). Simultaneous firing of particular transducer pairs or triplets may be used where amplitude is not additive.

Turning to FIG. 12A, another metapulse (344) is shown. Along the left margin, individual traces are labeled with designations for particular transducers of each array, for example “RT1” is right temporal #1 transducer, “OC1” is occipital #1 transducer, and so forth The figure represents one complete firing sequence of the headset, one cyclical “metapulse” (344), which repeats. One pulse train is fired from each of sixteen transducers in the course of a single metapulse. Thus the timeline can be viewed as a staggered chronology where a first transducer fires a first pulse train (343 a), a second transducer fires a second pulse train, and so forth, . . . and finally a last transducer fires a last pulse train (343 n) of the cycle, and the cycle can then begin again. By this means, selecting transducers from different arrays for consecutive actuation, the pulse trains strike the target anatomy like an “acoustic nudge”, each acoustic perturbation arriving from a somewhat differing direction as the metapulse cycles. A 6 KHz pulse train of 100 pulses has a duration of about 16 milliseconds, and could be termed a “nudge” for stimulating streaming. The cyclical repeated metapulse is thus a “super-nudge” composed of multiple “nudges,” each nudge a train of pulses.

Individual transducers may be directed at particular anatomical targets, but non-focused ultrasound used here spreads along its 6 dB beamwidth and strikes a broader target area at depth. FIG. 12A thus illustrates a three-dimensional patterned cyclical emission or “metapulse” of pulse train emissions from an array of sixteen crystals, where each crystal emission is directed in a unique general direction and is fired once per cycle. It can be said that the insonation regime is a cyclically repeating metapulse comprising one or more patterns of temporally modulated and spatially distributed pulse trains, each pulse train comprising multiple ultrasonic pulses. The insonation can thus be characterized as cyclically and stereotemporally modulated insonation. While not limiting in characterizing the invention, a headset with 16 transducers firing 16 millisecond pulse trains, one at a time, will cycle sequentially about every half a second. Mutatis mutandi, other permutations are possible by theme and variation around the concept of a pattern within a pattern within a pattern of temporally modulated and spatially distributed acoustic beams.

In general, patterned waveforms of programmed insonation comprise a train of pulses, each said pulses having a pulse duration of about 0.2 to 10 microseconds, more preferably about 1 to 8 microseconds, most preferably about 6 microseconds, in trains of pulses of 2 to 300 pulses per train, more preferably of about 100 to about 300 pulses per train, said train of pulses having a pulse repetition frequency of about 3 KHz to about 10 KHz, more preferably about 4 KHz to about 8 KHz, and most preferably about 6 KHz, with an amplitude measured as unattenuated peak rarefaction pressure P_(r0) of about 0.3 to about 1.0 MPa or more, and at a ultrasonic frequency of 0.5 to 3.5 MHz, more preferably about 0.8 or 0.9 to about 3.0 MHz, and most preferably about 1 MHz, or about 1.2 MHz, or about 2.0 MHz. The pulse trains are also vectored from multiple independently fired transducers, thus resulting in spatial modulation or distribution of the patterned waveforms.

An apparatus of the invention has program instructions that encode for autonomously driving a plurality of ultrasound transducers to emit a cyclically repeating metapulse, the metapulse comprising a wavepattern of spatially and temporally modulated pulse trains of ultrasound having a primary frequency f_(c), and an amplitude configured to achieve a P_(rAZsp) not to exceed 300 KPa, the pulse trains having a pulse repetition frequency corresponding to a duty cycle of 1-10%, more preferably 2-6%, and most preferably about 3 to 5% per transducer, the metapulse having a metapulse cycle repetition frequency of 0.25 to 10 Hz, until a stop instruction is received; thereby achieving low power consumption for extended portable operation independent of operator control and not requiring assisted cooling means.

The inventive devices may be built with multiple transducers formed as transducer arrays, each transducer array having a plurality of individually controlled piezoelectric crystals, permitting the emission of patterned meta-cycles of patterned pulse trains in complex modulations made possible by multiplexing a pulse generator signal or signals, for example across multiple logic gates actuated at selected clock frequencies as shown in FIGS. 10A-D as discussed above. In a preferred embodiment, the individual transducers may be about 1 cm in diameter or smaller and are spaced apart (unlike conventional phased array transducer assemblies) to permit heat dissipation between firings. The transducer crystals are not fired in pairs and the beams emitted are not convergent, but are instead fired individually in series under autonomous control of a remote controller unit, which contains a clock, pulse generator, logic circuits for transducer actuation, and optionally with control of amplitude of individual transducer output as compensation for attenuation or inter-transducer variability. This multiple mini-transducer approach has been proven to be safe, cognizant of the dangers of standing waves and heating, and is found to be surprisingly effective in sonothrombolysis. While not bound by theory, the device is thought to stimulate diffusion of r-tPA by insonation-induced fluid streaming in response to modulated pulsed ultrasound patterns directed at a target anatomy from multiple directions, where a first transducer is fired with a pulse train or “acoustic nudge”, a second transducer is then activated, and between each pulse of each pulse train, the emitted ultrasonic wavefront is allowed to fade in intensity. Taking into account a temporal-temporal or occipital-frontal beam path length of 10 to 15 cm in a typical application, the pulse interval is thus on the order of 1 to 2 microseconds, as was described in more detail in the preceding section. The overall “metapulse” may have a MCRF of about 2 Hz in the example of FIG. 12A and describes a complex modulated pattern of distributed pulses. The overall pattern or waveform is a cyclical pattern comprising spatially distributed and temporally modulated metapulses formed from sub-patterns of pulse trains and constitutes a regimen.

The apparatus may be programmed using instructions in EEPROM, for example, and may have a repertoire of regimens at its disposal that are selected in response to sensor data or altered according to predetermined criteria, and so forth. The apparatus may be configured for diurnal use for example, or individually tailored cyclical patterns are provided for prophylactic applications which may be switched to more intensive patterns in the event of a vascular stroke, mini-stroke, an increase in intracranial pressure, or transient ischemic attack, and so forth.

Other pulse and metapulse chronologies are readily conceived. FIG. 12B describes a metapulse sequence (346) where two metapulses are shown (repeating doublet pattern, left to right). Each metapulse consists of pulse trains fired by various pairs of transducers simultaneously. The doublet pairs selected for simultaneous firing are generally contralateral pairs so as to minimize potential additivity in the amplitude of the peak pressures where the beams meet. Study has shown that contralateral beams can be configured to overlap so that constructive addition of beam intensity is beneficial at target depths of 4 to 7 cm (for each hemisphere) and does not exceed safe limits at any depth. A total of 32 pulse trains are emitted in this example (345 a-345 n), but the invention is not limited thereto.

FIG. 12C describes a metapulse sequence (348) consisting of triplets and doublets, where three metapulses are shown (repeating pattern, left to right). Each doublet or triplet consists of simultaneous pulse train emissions by two or three transducers, respectively. Again these are chosen so that additive effects are minimized but are most beneficial at depth. By firing three transducers at once, where the individual transducers are selected from the right temporal, left temporal and occipital arrays, amplitudes do not rise above safe levels where beams overlap. A total of 48 pulse trains are emitted in this example (347 a-347 n), but the invention is not limited thereto.

Thus in selected embodiments, the apparatus is configured for emitting ultrasound in stereotemporal metapulses, each metapulse comprising a series of pulse trains emitted in a pattern selected from: a) a series of pulse trains emitted in sequence from a plurality of transducers, wherein only a single transducer is actuated according to a programmed order at any given time; b) a series of pulse trains emitted from pairs of transducers selected from a plurality of transducers, wherein only one pair of transducers is actuated according to a programmed order at any given time; c) a series of pulse trains emitted from triplets of transducers selected from a plurality of transducers, wherein only one triplet of transducers is actuated according to a programmed order at any given time; d) a series of pulse trains formed by actuating transducers in a sequential order, the series comprising any combination of singlet, doublet, or triplet transducer actuations; or, e) a series of pulse trains emitted on a carrier wave, the carrier wave having a sub-ultrasonic frequency of about 5 to 10 KHz, and most preferably about 6 KHz.

Individual arrays or transducers may be actuated more frequently than others, for example when it is desirable to preferably insonate a particular hemisphere of the brain or a frontal versus an occipital aspect of the cerebral vasculature. In other instances, particular transducers are chosen to fire more frequently than others so as to optimize acoustic streaming in a particular direction, such as circularly in the Circle of Willis by firing posteriorly-directed Rt temporal transducers in alternation with anteriorly-directed Lt temporal transducers in alternation, and then reversing the direction by firing anteriorly-directed Rt temporal transducers in alternation with posteriorly-directed Lt temporal transducers, so as to create clockwise and counterclockwise pressure gradients which stimulate directed acoustic streaming and flow. Also of interest are reciprocating pressure pulses, such as alternating pulse trains between matching transducers situated contralaterally in the temporal arrays, or orthogonally directed pulses in alternation from ipsilateral transducers of the temporal and occipital arrays, for example.

By firing only a few transducers at a time, and by firing individual transducers (as determined by the pulse repetition frequency) at a duty cycle in the 1 to 10% range, more preferably in the about 3 to 6% range, and in one embodiment with a duty cycle of about 3.6%, the need for assisted cooling is avoided. TI and thermal heating effects due to longer duty cycles are limited. This approach permits use of higher frequencies, which can be advantageous because mechanical index (MI) is more easily limited. Lower power consumption also results; without loss of efficacy. The apparatus is typically passively air-cooled, avoiding power consumption by fans, circulating coolant, and so forth.

The requisite pulse interval can be achieved with a pulse repetition frequency of about 4 to 10 KHz, more preferably about 5 to 8 KHz, and most preferably about 6 KHz.

Fortuitously, this PRF is more physiologically compatible than lower frequencies in that users have been observed to perceive pulsed insonation in the 2-4 KHz range, in particular, as an uncomfortable sound; paradoxically sensing, by a sort of biological demodulation, what is by definition an inaudible ultrasonic pulse. The 0.5 to 3.5 MHz primary frequency is well above the range of human hearing but can be “demodulated” when pulsed at 2-4 KHz.

FIG. 13 quantifies the threshold for audible sensation of ultrasound exposure as a function of a modulated pulse train frequency. Greater amplitudes are required to elicit a sensation outside the range of 0.2 to 4 KHz. In other words, pulse repetition frequencies greater than about 4 KHz are less likely to be perceived by the user. Frequencies in the 2-3 KHz range are most perceptible. Happily, selection of a 5 or a 6 KHz pulse repetition frequency solves this problem for most individuals and, at a duty cycle of 3 to 6% or so, poses no significant increase risk of excessive heating or overexposure as measured by T₁ and I_(sppa.3). At greater than 10 KHz PRF, overlap of successive wave patterns can be associated with standing waves, so 4-10 KHz has proved to contain a narrow range of comfort where safety is not compromised.

Also a parameter for safe operation is peak rarefaction pressure P_(r), a measure of acoustic pressure, and intensity. Care is taken in selecting parameters of pulse width, intensity and pulse repetition frequency not to exceed an I_(spta.3) limit of about 720 mW/cm². Control of acoustic pressure and intensity are achieved by adjusting the voltage applied to the transducer (V_(p-p)).

As shown in FIG. 14A, it can be seen that acoustic intensity (I_(sppa.0)) is a power function of voltage in tank studies. The relationship between P_(r) and voltage (V_(p-p)) is linear, as shown in FIG. 14B, where a representative curve at 1 MHz is shown. At any given frequency, for a desired peak rarefaction pressure in MPa, the voltage required can readily be calculated from a linear slope and intercept. Alternatively, a simple look-up table may be used to calculate the required voltage based on the acoustic pressure desired. Calibration data of this kind is specific for each individual transducer.

Individual transducer output can be modulated as shown in FIG. 10B, where the boost voltage V_(BANG) fed into transformer T1 is under control of the WIPER feedback voltage signal supplied to the voltage regulator. By supplying calibration data for each transducer to the microcontroller, the amplitude of the insonation pulse fed to each transducer is specific for that particular transducer. The apparatus operational flow chart of FIG. 15 takes advantage of this capability, which is an advance in the art, and permits the circuitry to compensate for the expected transducer-to-transducer variability seen in any manufactured product.

FIG. 15 shows functional steps (350) for automated operation of an apparatus where voltage is adjusted to compensate for transducer-to-transducer variability. Following attachment of the headset (351), the apparatus is powered on (352) and performs a startup self diagnostic. The apparatus then determines (353) the appropriate calibration factor for each individual transducer and increments (or decrements) a voltage correction for V_(BANG) as described in FIGS. 10A-B. If all systems are go, the apparatus commences (354) an insonation metapulse cycle of the kind illustrated in FIGS. 12A-C and continues this until powered down (355) or for a duration of time preset in the programming. The cycle may be repeated (356) if desired.

Insonation amplitude is directly related to peak rarefaction pressure, and the circuitry is configured to deliver no more than 300 KPa at z_(sp). FIG. 16A shows peak rarefaction pressure as a function of depth for selected increments in transducer voltage (V_(p-p)) from 30 to 80 V_(p-p). FIG. 16B plots the relationship between peak rarefaction pressure (KPa) and ICH conversion (%) as determined here from retrospective analysis of data from clinical trials. While not bound by theory, localized acoustic pressure intracranially, as correlated with maximal peak rarefaction pressure (360), is believed responsible for the increase in ICH over untreated baseline (361) shown in FIG. 16B. The relationship between applied acoustic pressure at the transducer face and resultant acoustic pressure at a depth in the skull is dependent on a complex analysis of attenuation. It can be seen that 300 KPa represents a threshold where increases in insonation amplitude are associated with increases in ICH conversion, a technological problem not previously recognized. Based on this analysis, a device configured not to exceed the P_(r)≦300 KPa threshold in target tissues was built. Coincidentally, this configuration operates for longer periods of time at lower power, and is found here to improve therapeutic outcomes, a technological advance in the art.

In a first example demonstrating the role of attenuation, FIG. 17A is a plot of peak rarefaction pressure (363) illustrating the effect of thick and thin skull phenotype as a function of depth at 1 MHz. Also shown is a curve for unattenuated emission (362). FIG. 17B is a curve fit for attenuation coefficient (A_(TempBONE)) versus frequency for temporal bone. Attenuation coefficient α is given in dB/mm-MHz.

FIGS. 18A and 18B represent physical models for analysis of an attenuation profile as a function of depth for a transducer seated at a temporal acoustic window (FIG. 18A) and for a transducer apposing an occipital acoustic window (FIG. 18B), where a layer of fatty tissue generally covers the muscles the spine that overlie the atlas and foramen magnum.

The outlines of a calculation of attenuation are first shown pictographically. The renderings represent physical models for analysis of an attenuation profile as a function of depth for a transducer seated at a temporal acoustic window (FIG. 18A) and for a transducer apposing an occipital acoustic window (FIG. 18B), where a layer of fatty generally covers the muscles the spine that overlie the atlas and foramen magnum.

Developing a temporal interface model (FIG. 18A) mathematically requires information about sound velocities and attenuation in the various tissue types. Tissue-specific attenuation constants can be approximated from literature values factored for measured thickness and the combined attenuation profile can then be calculated as a function of depth, where attenuation of P_(r) across a temporal acoustic window is given as (Eq 1):

${{P_{r}(z)}} = \frac{{PrA}_{z}}{{PrU}_{z}}$ where P_(r)(Z) is the ratio of attenuated (P_(rAz)) to unattenuated (P_(rUz)) ultrasonic pressure as a function of depth (z) in centimeters. Attenuation can be solved from Eq 2:

A_(TOTAL) = A_(SKIN) + A_(BONE) + A_(REFLECTION) + A_(BRAIN) ${or},{A_{TOTAL} = {{20 \cdot \log_{10}}\frac{P_{rAz}}{\Pr_{rUz}}}}$

And combining equations 1 and 2 yields (Eq 3),

$P_{rAz} = {P_{rUz}*10^{\frac{{(A_{SKIN})} + {(A_{BONE})} + {(A_{REFLECTION})} + {(A_{BRAIN})}}{20}}}$ where,

-   -   P_(rAz) is the attenuated peak rarefaction pressure at depth z         on the beam path;     -   P_(rUz) is the unattenuated peak rarefaction pressure at depth         z;     -   A_(SKIN) is the acoustic attenuation in the outer skin and         tissue;     -   A_(BONE) is the acoustic attenuation through the skull bone;     -   A_(REFLECTION) is the attenuation equivalent to reflection         losses at the interface between the inner surface of the skull         and the brain, nominally 3.02 dB;     -   A_(BRAIN) is an acoustic attenuation in the brain, typically a         constant at about 0.06 dB/mm-MHz;     -   z is a depth, the distance a ultrasonic beam wavefront has         traversed;     -   t_(SKIN) is the thickness of the outer skin and tissue layer;     -   t_(SKULL) is the thickness of the cranial bone proximate to the         transducer; and,     -   f_(c) is the center frequency (MHz).

Each component is now considered separately. The following attenuation coefficients, taken from the general literature, are tabulated for reference:

α_(TT) (dB/mm- Tissue Type MHz) Skin 0.18 Fat 0.04 Muscle 0.09 Sub-occipital brain tissue 0.09 Temporal brain tissue 0.08

Skin attenuation is typically small and may be neglected, but is given by (Eq 4): A _(SKIN)=(α_(SKIN) ·f _(c))·t _(SKIN)

Bone attenuation is significant and is dependent on thickness of the bone in the path of the transducer beam, frequency and is best described by a non-linear curve fit of physiological data. The attenuation for temporal bone (A_(TempBONE)) was derived by parabolic curve fit of available data (FIG. 17B) and is described mathematically as (Eq 5): A _(TempBONE)=(−0.186·f _(c) ²+3.257·f _(c)−1.51)*t _(SKULL).

The regression fit (R²) for this equation was 0.875.

Brain attenuation is given by (Eq 6): A _(BRAIN)=α_(BRAIN) ·t _(BRAIN)

Reflection attenuation at the SKULL:BRAIN interface is a function of the relative difference in acoustic impedance between the temporal bone and underlying brain tissue and is essentially a constant: A _(REFLECTION)=3.02 dB

Knowing bony layer thickness and having reference values for constant terms, the total attenuation plus reflection (K_(SKULL)) in decibels is readily determined. A similar measurement and calculation may be made for skin. In most instances, the attenuation associated with the outer skin layers is negligible compared to the larger contribution of the cranial bones, so equation 3 is further simplified to (Eq 7): P _(rAz) =P _(rUz) *K _(SKULL)*10^((A) ^(BRAIN) ^(*(z−t) ^(SKIN) ^(−t) ^(SKULL) ^()*f) ^(c) ^()/20) where P_(rAz) is the calculated pressure at depth z after tissue attenuation and P_(rUz) is the measured rarefaction pressure at depth z as measured in a tank of water.

This equation is readily solved by a calculating machine, such as a microcontroller with on-board math functionality when given skull thickness, and permits the device to predict P_(rAZsp) (peak rarefaction pressure at z_(sp)) as a function of depth based on a measurement of skull layer thickness such as by CT scan.

Turning to FIG. 18B, a physical model for analysis of an attenuation profile as a function of depth for a transducer seated at a sub-occipital acoustic window is described. The figure depicts a sub-occipital transmission path for ultrasonic energy into the cranial vault between the spinal column and the foramen magnum. The physiology is distinguished from the temporal window by a general absence of a boney layer, and attenuation is substantially lessened.

As the ultrasound pressure waves propagate from the transducer face to the point of maximum exposure in the cranium (it is assumed the primary mode of wave transmission is transverse, i.e. waves travelling parallel to the face of the transducer), the overall model for attenuation along the sub-occipital path can be approximated by evaluating the transmission characteristics across four major layers each with a tissue attenuation coefficient: Skin, fat, muscle, and brain tissue as shown in FIG. 18B.

Attenuation can be solved from Eq 8:

$A_{TOTAL} = {{A_{SKIN} + A_{FAT} + A_{MUSCLE} + A_{BRAIN}} = {{20 \cdot \log_{10}}\frac{P_{rAz}}{\Pr_{rUz}}}}$

And similarly as before (Eq 9),

$P_{rAz} = {P_{rUz}*10^{\frac{{(A_{SKIN})} + {(A_{FAT})} + {(A_{MUSCLE})} + {(A_{BRAIN})}}{20}}}$ where,

-   -   P_(rAz) is the attenuated peak rarefaction pressure at depth z         on the beam path;     -   P_(rUz) is the unattenuated peak rarefaction pressure at depth         z;     -   A_(SKIN) is the acoustic attenuation in the outer skin;     -   A_(FAT) is the acoustic attenuation through the bone;     -   A_(MUSCLE) is the attenuation through the fat layer;     -   A_(BRAIN) is an acoustic attenuation in the brain, typically a         constant at about 0.06 dB/mm-MHz;     -   z is a depth, the distance a ultrasonic beam wavefront has         traversed;     -   t_(SKIN) is the thickness of the outer skin layer;     -   t_(FAT) is the thickness of the fat layer;     -   t_(MUSCLE) is the thickness of the muscle layer; and,     -   f_(c) is the center frequency (MHz).

Each component is now considered separately. Attenuation coefficients (a), were previously tabulated (Table I).

Skin attenuation is typically small, but is given by (Eq 10): A _(SKIN)=(α_(SKIN) ·f _(c))·t _(SKIN) where thicknesses are on the order of 1 mm.

Fat tissue attenuation is given by (Eq 11) A _(FAT)=(α_(FAT) ·f _(c))·t _(FAT)

Based on empirical observation of experienced TCD sonographers, the total tissue thickness on the back of the neck will vary between 2 to 5 cm, of which 1 cm is muscle. Thus, the fat layer can vary between 1 to 4 cm.

Muscle tissue attenuation is given by (Eq 12) A _(MUSCLE)=(α_(MUSCLE) ·f _(c))·t _(MUSCLE)

Nominal muscle thickness is taken as 10 mm for most applications.

Brain attenuation is given by (Eq 6): A _(BRAIN)=α_(BRAIN) ·t _(BRAIN)

Because of the large variability in the fat layer and the variability in the point of maximum pressure (z_(sp)) depending on transducer selection, it is possible that the actual point of maximum peak negative pressure could be in an adjacent layer to the brain instead of in the brain itself.

If the fat layer on a patient is 1 cm thick, then the point of maximum peak negative pressure will certainly be inside the brain. Mathematically, if z_(sp)=3 cm, and the overlying layers of tissue are 2.1 cm thick (=0.1 cm+1 cm+1 cm) (skin+fat+muscle), P_(rAmax) is 0.9 cm into the brain tissue. P_(rAmax) is the point of maximum acoustic amplitude in tissue. The computation of attenuation is straightforward unless P_(rAmax) is situated in the connective tissue layers.

If z_(sp) is inside the fat or muscle layer, the estimate changes. In this case it is necessary to consider the total attenuation across the skin, fat, and muscle and then estimate the peak negative pressure at the muscle-brain tissue interface. This will be the estimated maximum peak negative pressure (P_(rAmax)) in brain tissue.

For most ultrasound systems, the peak negative pressure is conservatively assumed to decrease by about 0.5% per centimeter. Thus, the maximum peak negative pressure in the brain tissue (before accounting for the other attenuation values) can be estimated (for z_(sp)≦t_(SKIN)+T_(FAT)+T_(MUSCLE)) from (Eq 12): P _(r(Amax)) =P _(r(Uz) _(sp) ₎·(−0.05(t _(SKIN) +t _(FAT) +t _(MUSCLE))+(0.05z _(sp))+1)

And for z_(sp)>t_(SKIN)+t_(FAT)+t_(MUSCLE), P _(r(Amax)) =P _(r(Uz) _(sp) ₎

These considerations and calculations are useful in selecting conditions for operation of headsets of the invention.

FIG. 19 is a flow chart or logic diagram for automated operation of an apparatus (390) where transducer coupling is tested and verified before or during operation of the apparatus. Following attachment of the headset (391) to a skull, generally with gel on the transducers, the apparatus is powered on and performs a startup self diagnostic (392). The apparatus then determines (393) for each transducer whether the contact with the head is sufficient for efficient transmission of sound. If all systems are GO and acoustic coupling is verified, the apparatus commences (394) an insonation metapulse cycle and continues this until powered down (395) or for a duration of time preset in the programming. The cycle may be repeated if desired (396).

FIGS. 20A and B describe the use of phase angle θ to verify acoustic coupling. FIG. 20B plots voltage output corresponding to phase angle for a coupling verification circuit of FIG. 21. In this application, an ultrasound pulse may be used to validate acoustic coupling between the transducer interface and the underlying tissue target. If a transducer is not acoustically coupled to the underlying skull, generally with a couplant gel, the ultrasound bounces off the intervening air layer and fails to penetrate the skull. To verify coupling, in one embodiment, a voltage comparator circuit is used to measure phase angle of the voltage pulse activating the transducer. A high phase angle is indicative of poor coupling, generally indicating the presence of air between the transducer and the target tissue. A low phase angle indicates good coupling. These circuits are practical solutions to the problem of ensuring good acoustic coupling before initiating an autonomous ultrasonic pulse treatment regime. The microcontroller will verify that the phase angle does not exceed a preset threshold before initiating insonation.

As shown in FIG. 20A, an impedance matching system may be designed to match source and load impedances when the headset is properly seated and acoustically coupled on the cranium. The signal source in this application is an amplified clock frequency emitted in pulses and the load is a piezoelectric transducer.

In considering an ultrasound transducer with a capacitive reactance, overall power load impedance is the sum of a real resistance “R” and an imaginary reactance “−jX”. Current is shifted in phase by an angle θ relative to voltage.

Total impedance Z_(mag) is calculated as: Z _(LOAD) =R−j/ωC where R is resistance in ohms, ω is frequency expressed as radians, ω=2πf, where f is the frequency in Hz, and C is capacitance expressed in Farads, which may also be written, Z=√{square root over (R ² +X _(C) ²)} where X_(C) is the capacitive reactance (ohm).

Taking the RC network and assigning the real part of the impedance to the real axis and the imaginary part to the imaginary axis, the impedance vector Z_(mag) will appear as in FIG. 20A.

The Pythagorean relationships for right angle triangle geometry, relating ordinate R, abscissa X_(C) and hypotenuse Z, allows the impedance Z_(mag) to be solved from the resistance and the capacitive reactance X_(C). However, all that is needed to determine whether the surface of the transducer is acoustically coupled to an external load is the phase angle θ. The phase angle (θ_(OPEN)) will be large (ie. capacitive reactance will be large) when the transducer is acoustically mismatched with air, and will be dramatically lower (θ_(COUPLED)) when the transducer is acoustically matched with the tissue of the skull. This observation is illustrated in FIG. 20A. Thankfully, full measurement of the change in complex impedance (in phasor notation, Z_(mag)∠θ for Z₁, Z₂) when coupling is established is not necessary for detection of an operative level of acoustic coupling between the crystals and the head of the subject wearing the headset. A rapid check of phase angle may be made by emitting an acoustic pulse and assessing phase angle of the pulse in a transducer. A circuit for digitally reporting the phase angle to a microcontroller is sufficient to assess acoustic coupling and the microcontroller can be programmed to perform this test individually for each transducer without operator intervention. If a transducer is not coupled, the operator will have to readjust the fit of the headset on the wearer, or eliminate any air between the transducer and the skin by adding gel couplant for example.

As shown in FIG. 21 schematically, implementation of circuitry (400) for phase measurement on a transducer load (403) driven by an oscillator (402) may be performed with an integrated circuit having a phase comparator, such as the HCT2046A (Philips Semiconductor, see 1997 Datasheet), which contains an edge triggered RS-type flip-flop phase comparator (PC3).

The average output from phase comparator (401), fed to a voltage comparator via the low-pass filter and seen at the demodulator output at pin 10 (405, V_(PHASE)), is the result of the phase differences of SIG_(IN) and COMP_(IN) are generally linear between 0 and 360 degrees theta as shown in FIG. 20B.

The output from R_(SENSE) (404) can be offset to produce a desirable VPHASE=0 at zero degrees. More details of the device are provided in the 74HC/HCT4046A Phase-Lock-Loop with VCO IC data sheet from Philips.

The realization of these considerations is a phase detection circuit with linear output voltage that can be digitally encoded to flag an uncoupled transducer in a headset array for corrective action, as is needed for use of the device by relatively unskilled technicians or for self-use. A simple LED may be used to indicate an uncoupled transducer, for example.

In autonomous operation of an apparatus configured for detection of acoustic coupling under each transducer prior to initiation of insonation, the apparatus will fault if coupling requires adjustment.

A variety of watchdog circuits to verify proper function before initiating insonation may be employed. Status lights or other indicator such as sounds, buzzers, LEDS, or even a liquid crystal display may be used to communicate the readiness of the device to begin ultrasound emissions. The LCD may for example scroll a message indicating that one of the transducers is not properly seated on the head. Status displays may also include battery status indicators, temperature sensors and indicators, and the like. Circuit fault detectors within the skill of those who practice electronic arts may also be incorporated.

Generally, frequency is also known, or easily measured, permitting use of Z_(mag)∠θ information in other calculations, such as time of flight, which may be utilized in rudimentary imaging of midline shift conditions and quantitation of total dosage (from measurement of transducer-to-transducer pulse reception).

Now, turning to the biology and the range of vascular and neurological conditions where ultrasound has a role in thrombolysis, FIG. 22 depicts schematically the competing cycle of fibrinogenesis (coagulation) and fibrinolysis (thrombolysis). Clotting is an excess of fibrinogenesis, results in deposition of insoluble fibrin strands from fibrinogen, and requires conversion of prothrombin to thrombin. Clot lysis is initiated by the presence of fibrin strands and requires the conversion of plasminogen to plasmin.

FIG. 23 is a schematic of the major limbs of the classical coagulation model. Both the Intrinsic Pathway and the Extrinsic Pathway join as a common pathway at activation of Factors IX and X, which are involved in propagating coagulation. Formation of a fibrin clot from fibrinogen requires thrombin and also Factor XIII (von Willebrand's factor) which binds to the nascent clot and promotes clot retraction through a process of activating a transglutaminase that acts on the fibrin strands.

Deposition of fibrin also attracts binding of plasminogen activator, which recruits plasminogen for conversion to the active serine protease plasmin that is active in reducing fibrin to small fragments known as fibrin split products.

FIG. 24 is a schematic of the “cellular model” of coagulation (after Monroe 2001 Thromb Haemost 85:958-965). Earlier conceptions had focused on soluble molecules active in coagulation, as were readily studied in the test tube, but overlooked essential cellular roles played by platelets in particular as scaffolding, toolboxes, supply cabinets and workbenches for coagulation reactions, but also leukocytes, macrophages, and endothelial cells in their essential role as promoters of fibrinolysis. Shown here are three key stages of coagulation, termed “initiation”, “amplification”, and “propagation”. In the propagation phase, large scale conversion of prothrombin (PT) to thrombin leads to rapid and overwhelming deposition of fibrin.

FIG. 25 depicts fibrinolysis involving endogenous tissue plasminogen activator (e-tPA) and ultrasound. Binding of endogenous tPA to fibrin strands results in formation of plasmin from plasminogen and subsequent digestion of the clot. Ultrasound is believed to promote clot breakdown by induced acoustic streaming, where fibrin strands are loosened and fluid with soluble mediators of clot lysis is brought into contact with the newly exposed fibrin surfaces. The mechanism of action in which ultrasound accelerates thrombolysis is thought to rest with acoustic streaming, defined as movement of fluid induced by ultrasound (Sakharov et al. 2000). This streaming is essentially a mild stirring of fluids around the clot, which accelerates diffusion of macromolecules and fibrin split products, and exposes new clot surfaces for attack. As ultrasound output power and peak negative pressures are raised, this stirring action increases.

Earlier reports indicated partial success with highly focused ultrasound, where individual clots were visualized using TCCD and then insonated at 2 MHz at about 400 mW/cm² (Cintas et al, 2002, High Rate of Recanalization of Middle Cerebral Artery Occlusion During 2-MHz Transcranial Color-Coded Doppler Continuous Monitoring Without Thrombolytic Drug, Stroke 33; 626-628). This study required precise sonographic positioning of the transducer and focused insonation at the precise site of the clot.

Surprisingly however, unfocused transcranial ultrasound, modulated temporally and spatially as described here, is useful without exogenous administration of r-tPA. Modulated ultrasound is directed at the cerebral vasculature as a whole from multiple directions (i.e. spatially distributed modulation) in a series of patterned pulse trains, what is essentially a pattern within a pattern within a pattern, where pulse trains of pulses are emitted from individual non-focused transducers and a plurality of transducers of a plurality of arrays are fired in a patterned sequential order (i.e., as a metapulse, which are spatially and temporally patterned pulse trains of pulses). Ultrasound may be provided in this way without specific information about the presence or location of a clot and may also be performed prophylactically without a diagnosis if desired.

FIGS. 26A and 26B depict a model for vascular vasodilation with release of endogenous nitric oxide, where blood shear (FIG. 26A) is replaced by ultrasound (FIG. 26B). This model predicts that the ultrasound device of the present invention will have a positive effect as a standalone apparatus for non-invasive treatment of a variety of conditions, including migraine, headache, intracranial hypertension, hydrocephalus, and so forth, and may increase blood flow to the brain so as to improve delivery of a variety of parenteral and oral drug formulations.

The structural members of the headset of the device are built entirely from plastic and the electronics are isolated from the headset so that the headset may be operated under remote control, thus permitting insertion of the headset into a CT or MRI machine during operation. Transverse sectional views as shown in FIGS. 27A and 27B may be obtained.

While the above is a complete description of selected embodiments of the present invention, it is possible to practice the invention use various alternatives, modifications, combinations and equivalents. All of the U.S. patents, U.S. patent application publications, U.S. patent applications, foreign patents, foreign patent applications and non-patent publications referred to in this specification are incorporated herein by reference in their entirety. In general, in the following claims, the terms used should not be construed to limit the claims to the specific embodiments disclosed in the specification and the claims, but should be construed to include all possible embodiments along with the full scope of equivalents to which such claims are entitled. Accordingly, the claims are not limited by the disclosure.

Example I

Fifteen healthy volunteers were fitted with an apparatus of the invention. Modulated ultrasonic insonation was actuated according to autonomous instructions embedded in EEPROM memory of the device and continued while monitoring vascular and neurological status. Specific parameters for the ultrasonic wavepattern are generally as disclosed above. The insonation was continued for two hours without adverse effects. No adverse effects were reported in any of the tests.

Example II

In one aspect of the invention, a headset is realized that permits users to target critical vasculature without special imaging studies: i.e., simply by fitting the headset onto the skull according to craniological landmarks that define a reference plane and the location of the major arteries. Studies were undertaken to determine what level of targeting was achieved. Transducer arrays of the headsets of the invention were modified to permit transcranial Doppler monitoring, where the “on-target” aim of the insonation was scored by detection of Doppler signals from the target vasculature. In a preliminary study, a review of case reports revealed that 86% of patients had detectable Doppler waveforms in the MCA and related cerebral vasculature. An average of 4.1 transducers received a return signal, indicating that multiple transducers were on target. In a second study, MCA-localized Doppler was detected in 100% of all subjects; on average, 5.8 of the 12 temporally disposed transducers received Doppler return signals from the targeted MCA region and 2.7 of 4 transducers in the suboccipital array received Doppler return signals from the targeted Basilar Artery. Combining the studies, 91% of the subjects showed evidence that the headset transducer arrays were correctly targeting the cerebral vasculature nexii of interest. The function of the headset to achieve rapid, unassisted, “passive” stereotactic targeting of the ultrasonic transducers onto key vascular targets is a factor in this success.

While representative, the data of these examples is not intended to limit the invention to a particular wavelength, modulated insonation pattern, intensity, or one particular transducer array geometry. One skilled in the art will discover that certain insonation patterns or frequencies are more effective than others and that modifying the geometry or number of transducers in the arrays will achieve incremental improvements. Improvements in 90 day outcomes are obtained by periodic follow-up treatment with ultrasound (without r-tPA) over a period of several days or weeks following an ischemic attack, and in fact the headset can be use prophylactically by itself if needed because of its capacity to non-invasively actuate endogenous mediators of thrombolysis.

INDUSTRIAL APPLICABILITY

The ultrasonic cerebral infarction therapeutic apparatus of this invention is an apparatus that dissolves thrombus responsible for cerebral infarction by irradiating the affected tissue with repeating cycle of ultrasonic wave patterns. The apparatus is useful for non-surgical application of ultrasound in ischemic stroke and, with superficial modification, for infarcted or embolic conditions of other vascular structures.

In one embodiment, the apparatus functions autonomously without intervention, essentially as a pre-programmed automaton for delivering transcranial ultrasound, but optionally with sensors for collecting data and for adjusting operating parameters accordingly.

In a first sensor mode, a transcranial ultrasound apparatus is configured with a phase detection circuit for verifying acoustic coupling before actuation of ultrasonic emissions.

In another mode, a transcranial ultrasound apparatus is configured for adjusting V_(BANG) using data on transducer voltage response. Using a multiplexed driving signal or signals, ultrasound is emitted by a plurality of transducers of an array while varying voltage to each individual transducer on the fly, thus improving reproducibility and consistency of insonation, which can be irregular due to variations in transducer manufacture.

INCORPORATION BY REFERENCE

All of the U.S. patents, U.S. patent application publications, U.S. patent applications, foreign patents, foreign patent applications and non-patent publications referred to in this specification and related filings are incorporated herein by reference in their entirety.

While the above is a complete description of selected embodiments of the present invention, it is possible to practice the invention use various alternatives, modifications, combinations and equivalents. In general, in the following claims, the terms used should not be construed to limit the claims to the specific embodiments disclosed in the specification and the claims, but should be construed to include all possible embodiments along with the full scope of equivalents to which such claims are entitled. Accordingly, the claims are not limited by the disclosure. 

We claim:
 1. An apparatus for autonomous operation in a non-invasive, transcranial ultrasound (US) mode, said apparatus comprising an electronic circuit with microcontroller, clock, memory, instruction set, a portable power and voltage supply, and on/off control, wherein said circuit is configured for actuating a headset on which are disposed a plurality of ultrasonic transducer arrays, each array having a plurality of ultrasonic transducers externally disposed on a skull and acoustically coupled thereto; said headset, when positioned on a subject's head for transcranial sonothrombolysis, defining a headset plane that is inclined with respect to a horizontal reference plane by 10 to 15 degrees and is parallel to a plane defined by the subject's Circle of Willis, further characterized in that said headset is configured with a nosepiece having a fixed end affixed to the headset at the front and a second end and protruding transversely to the headset plane and along the subject's forehead and with contralateral right and left earpieces corresponding to opposite sides of the subject's head and slidably and removably mounted on an internal surface of said headset, and left (Lt) and right (Rt) temporal transducer arrays respectively juxtaposed to said earpieces; and a posterior occipital transducer array, from the set of transducer arrays, is disposed at a back portion of the headset in proximity to the occipital acoustic window under the occipital prominence when said headset is circumcranially tightened around said skull such as to direct corresponding US beams at the basiliar and vertebral artery and a junction of the internal carotids of the Circle of Willis, said nosepiece and earpieces forming a triad of registration surfaces of an Isosceles triangle which defines a foundational reference plane containing a sphenoid shelf and the Circle of Willis of said skull, said triangle having a base, an apex, and a midline, said triangle for stereotactically positioning said headset and for stereotactically aligning said transducer arrays to additionally insonate a vasculature of said Circle of Willis and the cerebral arteries projecting therefrom, wherein said nosepiece and contralateral earpieces are configured such that, when the headset is positioned on the subject's head for transcranial sonothrombolysis, said contralateral earpieces self-align the respective left and right temporal transducer arrays with the otobasion superior and the sphenoid shelf without (i) a need for measuring or locating of said otobasion superior and sphenoid shelf prior to positioning of the headset on the subject's head and (ii) a need for diagnostic imaging guidance.
 2. The apparatus of claim 1, wherein said headset comprises a first, second and third registration surface for engaging one each the nasion, left otobasion superius, and right otobasion superius craniological landmarks of said skull so as to stereotactically align said transducer array or arrays of said headset with an intracranial target or targets without need for diagnostic imaging guidance and wherein each transducer of said transducer arrays is independently operable.
 3. The apparatus of claim 1, wherein said headset comprises: a) an anterior headframe member configured for spanning ear to ear across the brow of said skull; said anterior headframe member generally “U-shaped” in form, with first end and second end contralaterally disposed thereon; b) a posterior headband member configured for spanning ear to ear under the occipital protuberance of said skull, said posterior headband having two ends, wherein each said end is configured for inserted into one apposing end of said anterior headframe member, said anterior headframe member further comprising a tensioning mechanism for engaging said ends of said posterior headband member and tightening said headset circumcranially around said skull; c) a nasion registration bracket disposed anteriorly at a midpoint on said anterior headframe member and a nasion registration pad pendant therefrom, said nasion registration pad forming said first registration surface for engaging said nasion craniological landmark and offsetting said midpoint of said anterior headframe member by a height h₁; d) a pair of otobasion superius registration members slideably disposed contralaterally on said anterior headframe member, said Rt otobasion superius registration member forming said second registration surface and said Lt otobasion superius registration member forming said third registration surface; and further wherein said headset is obliquely inclined relative to said foundational reference plane by said height h₁ anteriorly so that said anterior headframe member is raised above the eyes of said skull, has clearance around the ears of said skull, and wherein said posterior headband member is obliquely inclined below said reference plane by a height h₂, thereby engaging the underside of said occipital protuberance of said skull when stereotactically positioned thereon.
 4. The apparatus of claim 3, wherein each said registration surface of said otobasion superius registration member is an earpiece, and said Rt earpiece is fixedly mounted in relation to a Rt temporal transducer array and said Lt earpiece is fixedly mounted in relation to a Lt temporal transducer array, said earpieces each having dimensions for stereotactically positioning each said temporal transducer array in acoustic contact with a temporal acoustic window when said nasion registration pad is seated on said nasion and said each earpiece is seated on one said otobasion superius.
 5. A kit for sale with an apparatus of claim 1, which comprises a set of transducer arrays in a disposable module, each said transducer array being prefitted with a ready-to-use gel couplant pad, and wherein each said disposable module is configured for activation by insertion into a mated receptacle on said headset, and optionally wherein said apparatus is provided with functional self-check circuitry enabled to verify acoustic coupling of said transducer arrays prior to initiation of cyclical metapulse emission. 